hydrogels and composite material containing hydrogels and liposomes dispersed therein, which exhibit a reduced friction coefficient compared to neat hydrogels or composites containing hydrogels, processes for preparing the same, and methods for using the same are disclosed.
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1. A composition comprising a hydrogel or a composite material containing a hydrogel, and a plurality of liposomes dispersed throughout the bulk of said hydrogel, the composition being characterized by a shear storage modulus (G′) of at least 2000 Pa at a temperature of 25° C. and a frequency of 1 hz,
wherein:
an average diameter of said liposomes is larger than 80 nm, said average diameter being a z-average determined by dynamic light scattering; and/or
a degree of crosslinking of said hydrogel is higher than 0.2 molar percent, wherein said crosslinking comprises covalent crosslinking,
and wherein a concentration of cholesterol in said liposomes is less than 40 molar percent relative to a total lipid amount of said liposome.
2. The composition or composite of
3. The composition or composite of
4. The composition or composite of
5. The composition or composite of
6. The composition or composite of
8. The composition of
9. The composition or composite of
10. The composition or composite of
11. The composition or composite of
12. The composition or composite of
14. The composition or composite of
15. The composition or composite of
mixing an aqueous suspension of said liposomes with a hydrogel-forming agent in the presence of a covalent crosslinking agent,
thereby obtaining the composition or composite.
18. The article-of-manufacturing of
19. A method of treating a living organism suffering from a medical condition associated with loss of or damaged cartilage, comprising replacing at least a portion of said cartilage with the composition or composite of
20. The method of
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This application is a continuation of U.S. patent application Ser. No. 15/890,504 filed on Feb. 7, 2018, which is a division of U.S. patent application Ser. No. 14/902,574 filed on Jan. 3, 2016, now U.S. Pat. No. 9,901,660, which is a National Phase of PCT Patent Application No. PCT/IL2014/050604 having International Filing Date of Jul. 3, 2014, which claims the benefit of priority under 35 USC § 119(e) of U.S. Provisional Patent Application No. 61/842,995 filed on Jul. 4, 2013.
The contents of the above applications are all incorporated by reference as if fully set forth herein in their entirety.
The present invention, in some embodiments thereof, relates to material science, and more particularly, but not exclusively, to compositions and methods for reducing the friction coefficient of hydrogels or of composite materials comprising a hydrogel, and to uses of such low friction hydrogels or composite materials containing same.
Lubrication in aqueous media presents a critical challenge in modern material science. Lubrication in aqueous and biological media is often problematic as water on its own is not a good lubricant, while surfaces or surface coatings in water frequently exhibit quite high friction coefficients, higher than 0.08, especially at high loads/pressures. The problem is more evident when extremely low friction is required, particularly at high pressures of up to 100 atmospheres or more, and at low sliding velocities.
Various attempts to provide low friction conditions in aqueous media, and particularly under physiological conditions for treating, inter alia, joint dysfunction, have been made.
Vecchio et al. [Rheumatology (Oxford), 1999, 38(10), pp. 1020-1021] describe the injection of dipalmitoylphosphatidylcholine (DPPC) lipid surfactant solutions in propylene glycol into joints in an attempt to provide a treatment for osteoarthritis.
U.S. Pat. No. 6,800,298 describes a lubricating composition (i.e. a lubricant) comprising dextran-based hydrogel with lipids.
Liposomes are vesicles whose membranes in most cases are based on phospholipid bilayers. They are generally biocompatible and, when modified with other molecules, are widely used in clinical applications, primarily as drug delivery vehicles, as well as in gene therapy and for diagnostic imaging.
WO 2008/038292 discloses, inter alia, multilamellar vesicles or liposomes (MLVs) of several phospholipids above their liquid-crystalline-phase to gel-phase transition temperature (Tm) as possible boundary lubricants in the articular cartilage environment.
WO 2011/158237, by some of the present inventors, discloses, inter alia, a method for lowering the friction coefficient of surfaces, which is effected by applying gel-phase liposomes onto surfaces to form a boundary lubricant layer, wherein the temperature of the surface at the time of lubrication is below the phase transition temperature (Tm) of the liposomes. The described method is suitable for lubricating biological and non-biological surfaces, including the surfaces of a biological tissue in a mammalian subject, e.g., for treating joint dysfunction.
Further studies on surface lubrication by liposomes are described in, for example, Klein et al., Faraday Discuss., 1994, 98, p. 173-188; Goldberg et al., Advanced Materials, 2011, 23(23), p. 3517-3521; Goldberg et al., Chemistry and Physics of Lipids, 2012, 165, p. 374-381; and Goldberg et al., Biophys. J., 2011, 100(10), p. 2403-2411.
A hydrogel is composed of a three-dimensional fibrous network containing up to 99.9% water. Swelling, or uptake of water, is made possible due to the hydrophilic groups attached to the polymer backbone of such hydrogels. The polymer strands may be chemically crosslinked to various extents between groups in the backbone or side-chains, giving rise to a variety of mechanical properties of the hydrogel. Hydrogels can be biocompatible and based on their synthetic or natural occurring polymeric components, can be biodegradable (e.g., by enzymes) or non-biodegradable. These characteristics gave rise to a great interest from the biomaterial field developing many bio-gels based applications including hydrogel-based scaffolds for tissue engineering applications. Among them are the calcium alginate microcapsules [Lim et al., Science, 1980, 210(4472), p. 908-910], alginate hydrogel for myocardial repair [Ruvinov et al., Biomaterials, 2011, 32(2), p. 565-578], and polyethylene glycol hydrogels for neural tissue [Mahoney et al., Biomaterials, 2006, 27(10), p. 2265-2274].
Poly-HEMA-based hydrogel is biocompatible and its water content could reach more than 70%, resembling that of cartilage. Its Young's modulus may be 1 MPa, depending on the exact hydrogel composition, also similar to that of cartilage. Hence, hydrogels based on polymeric constituents such as poly(2-hydroxylethylmethacrylate) (pHEMA) have been investigated for use as synthetic cartilage replacement substance [Petrtyl et al., Acta of Bioengineering and Biomechanics, 12 (3), 2010].
In a study on the tribological properties of pHEMA-based hydrogels for use in artificial cartilage [Bavaresco et al., Wear, 2008, 265(3-4), p. 269-277], the friction coefficient and wear as a function of different crosslinking densities, crosslinking agents, sliding speed and contact pressures were investigated.
Freeman et al. [Wear, 2000, 241(2), p. 129-135] studied the tribological behavior of pHEMA surface to a stainless steel ball as a function of the load, lubrication, crosslinking density and the degree of the hydrogel hydration.
Gong et al. [, Soft Matter, 2006. 2(7), p. 544-552] reported the effect of adding surfactants to the water medium on the friction coefficient of a negatively charged polyelectrolyte hydrogel in a parallel-plate rheometer configuration up to low pressures around 1 atm.
Gulsen et al. [Current Eye Research, 2005, 30, p.1071-1080] teach contact lens compositions with drug delivery capabilities, and specifically teach dispersing exceptionally small dimyristoylphosphatidylcholine (DMPC) SUV liposomes (less than 50 nm or 80 nm in diameter) in poly-2-hydroxyethyl methacrylate (p-HEMA) hydrogels, which are a common contact lens material. The results of this study show that the p-HEMA gels loaded with exceptionally small liposomes are transparent and that these gels release drugs for a period of about 8 days.
DiTizio et al. [Biomaterials, 1998, 19, p. 1877-1884] teach a liposomal soft hydrogel system that reduces bacterial adhesion to silicone catheter material.
Nagarsenker et al. [International Journal of Pharmaceutics, 1999, 190, p. 63-71] teach liposomes dispersed in soft polycarbophil gel.
Mourtas et al. [Langmuir, 2009, 25(15), p. 8480-8488] teach rheological properties of complex soft and semi-solid hydrogels containing different amounts of liposomes and/or cyclodextrin.
Kang et al. [Journal of Drug Targeting, 2010; 18(8), p. 637-644] teach cationic liposomes composed from less than 50% phosphtidylcholine lipids, dispersed in a soft thermosensitive gel.
Mechanical properties of layers of stable liposomes attached onto solid surfaces, including surfaces of hydrogels, were studied by atomic force microscopy (AFM) force measurements [Brochu, Ph.D. Thesis in the Université de Sherbrooke, Canada, 2008, Id.: 50177338].
Additional prior-art documents include U.S. Patent Application Publication Nos. 20040171740, 20060270781 and 20110293699, and U.S. Pat. Nos. 7,638,137 and 8,273,366.
The present inventors have uncovered that incorporation of liposomes within hydrogels result in substantial reduction of the friction coefficient of the hydrogels and have therefore designed and successfully practiced compositions comprising a hydrogel, or a composite material comprising the hydrogel, and liposomes, in which the liposomes are dispersed within the hydrogel. Hereinafter, the term “hydrogel” refers also to a composite material containing a hydrogel, unless specified otherwise. The present inventors have demonstrated that these compositions exhibit a substantially reduced friction coefficient as compared to the hydrogel (or a composite material containing same) per se (without the liposomes) and hence can be utilized in various applications in which hydrogels that exhibit low friction coefficient are desired.
According to an aspect of some embodiments of the present invention, there is provided a composition which includes a hydrogel or a composite material containing a hydrogel, and a plurality of liposomes dispersed throughout the bulk of the hydrogel, the composition being characterized by a dynamic shear storage modulus (G′) of at least 1000 Pa, wherein:
an average diameter of the liposomes is larger than 80 nm; and/or
a degree of crosslinking of the hydrogel is higher than 0.2 molar percent.
According to some of any of the embodiments described herein, the concentration of the liposomes is higher than 4 mM.
According to some of any of the embodiments described herein, the average diameter of the liposomes is larger than 80 nm.
According to some of any of the embodiments described herein, the degree of crosslinking of the hydrogel is higher than 0.2 molar percent.
According to some of any of the embodiments described herein, the degree of crosslinking of the hydrogel is 0.2 molar percent or lower.
According to some of any of the embodiments described herein, the concentration of the liposomes is higher than 4 mM, whereby the degree of crosslinking of the hydrogel is higher or lower than 0.2 molar percent.
According to some of any of the embodiments described herein, the concentration of the liposomes is 4 mM or lower, whereby the degree of crosslinking of the hydrogel is higher or lower than 0.2 molar percent.
According to some of any of the embodiments described herein, the concentration of the liposomes is 4 mM or lower, whereby the degree of crosslinking of the hydrogel is higher or lower than 0.2 molar percent.
According to some of these embodiments, the degree of crosslinking of the hydrogel is higher than 0.2 molar percent.
According to some of any of the embodiments described herein, the average diameter of the liposomes is 80 nm or lower.
According to some of these embodiments, the concentration of the liposomes is higher than 4 mM.
According to some of these embodiments, the concentration of the liposomes is 4 mM or lower.
According to some of any of the embodiments described herein, the degree of crosslinking ranges from 0.5 molar percent to 8 molar percent.
According to some of any of the embodiments described herein, the diameter of the liposomes is greater than 100 nm.
According to some of any of the embodiments described herein, the diameter ranges from 100 nm to 700 nm.
According to some of any of the embodiments described herein, the diameter ranges is larger than 700 nm.
According to some of any of the embodiments described herein, the liposomes further comprise an additional agent selected from the group consisting of a polymer, a hydrogel-forming polymer, cholesterol, a liposome-stabilizing agent, a labeling agent, a bioactive agent and a therapeutically active agent.
According to some embodiments, the additional agent is a polymer, and according to some embodiments it is a hydrogel-forming polymer.
According to some embodiments, the polymer is selected from the group consenting of poly(2-hydroxyethyl methacrylate) (pHEMA), alginate and hyaluronic acid (HA).
According to some embodiments of any of embodiments of the present invention, the additional agent is cholesterol.
According to some embodiments, the concentration of the cholesterol ranges from 1 molar percent to 50 molar percent relative to a total lipid amount of the liposome, or lower.
According to some embodiments, the concentration of cholesterol is 40 molar percent or lower, relative to a total lipid amount of said liposome.
According to some embodiments, the concentration of cholesterol ranges from 1 molar percent to 15 molar percent relative to a total lipid amount of said liposome.
According to some embodiments, the concentration of cholesterol ranges from 5 molar percent to 10 molar percent relative to a total lipid amount of said liposome.
According to some of any of the embodiments described herein, the hydrogel is formed of a hydrogel-forming agent being selected from the group consisting of hydroxyethyl methacrylate (HEMA), hydroxyethyl acrylate (HEA), acrylamide (AAm), methacrylamide (MAAm), acrylic acid (AAc), methacrylic acid (MAAc), hydroxyethyl acrylate (HEA), hexyl methacrylate, N-isopropylacrylamide (NiPAAm)), N-isopropylmethacrylamide, polylactic acid, polyamide, polyethylene-terephthalate (PET), polyvinyl alcohol, polyurethane, polycaprolactone, polyethylene-glycol (PEG), polyethyleneoxide dimethacrylate (PEOdMA), N,N-dimethacrylamide (nnDMAA), hyaluronic acid (HA), HA methacrylate, peptides, saccharides, gelatin, gelatin methacrylate, chitosan, chitosan methacrylate, glycol chitosan, glycol chitosan methacrylate, alginate, alginate methacrylate, cellulose, siloxanes, polysiloxanes, and any oligomer and/or polymer thereof, in any combination thereof.
According to some of any of the embodiments described herein, the hydrogel is formed of hydroxyethyl methacrylate (HEMA) and/or poly hydroxyethyl methacrylate (pHEMA).
According to some of any of the embodiments described herein, the hydrogel further comprises a hydrogel-forming agent which is selected from the group consisting of methacrylic acid, methacrylamide, polyethyleneoxide dimethacrylate, acrylamide and N,N-dimethacrylamide (nnDMAA).
According to some of any of the embodiments described herein, the hydrogel is formed of gelatin methacrylate.
According to some embodiments, a degree of methacrylation in the gelatin methacrylate ranges from 10 percents to 90 percents.
According to some embodiments, the degree of methacrylation in the gelatin methacrylate is 75 percents.
According to some embodiments, the composition as described in any one of the embodiments herein, and any combination thereof, is in a dry form.
In some embodiments, the dry form of the composition can be re-hydrated.
According to another aspect of some embodiments of the present invention, there is provided a process of preparing the composition as described herein, in any one of the embodiments thereof, and any combination thereof, the method comprising mixing an aqueous suspension of the liposomes with a hydrogel-forming agent, as described in any of the respective embodiments herein, in the presence of a crosslinking agent (which optionally can form a part of the hydrogel-forming agent), thereby obtaining the composition.
According to some of any of the embodiments of this aspect of the present invention, the suspension further comprises an initiator.
According to some of any of the embodiments of this aspect of the present invention, the suspension further comprises a catalyst.
According to some of any of the embodiments of this aspect of the present invention, the process further comprises dehydrating the composition.
According to some of any of the embodiments of this aspect of the present invention, the process further comprises, subsequent to the dehydrating, rehydrating the composition.
According to some of any of the embodiments of this aspect of the present invention, the crosslinking agent is selected from the group consisting of poly(ethylene glycol)n dimethacrylate (EGDMA), polyethyleneoxide dimethacrylate (PEOdMA), N,N′-methylenebisacrylamide (MBA or MBAm), N,N′-methylenebis(2-methylacrylamide), methylene diacrylate, methylene bis(2-methylacrylate), diethylene glycol diacrylate, hexamethylene diacrylate, oxybis(methylene) bis(2-methylacrylate) and oxybis(ethane-2,1-diyl) bis(2-methylacrylate).
According to an aspect of some embodiments of the present invention, there is provided a composition prepared by the process described herein, in any one of the embodiments thereof, and any combination thereof.
According to some of any of the embodiments of the present invention, the composition presented herein is characterized by a dynamic friction coefficient in aqueous medium that ranges from 0.001 to 0.08 under a pressure of at least 1 atmosphere.
According to some of any of the embodiments of the present invention, the composite material comprises a material selected from the group consisting of a woven mesh of fibers, non-woven fibers, a plurality of rods and a net.
According to some of any of the embodiments of the present invention, the composition is characterized by a dynamic friction coefficient in aqueous medium that ranges from 0.001 to 0.08 under a pressure of at least 1 atmosphere.
According to another aspect of embodiments of the present invention, there is provided a method of lowering a friction coefficient of a hydrogel or of a composite material containing a hydrogel, the method comprising forming the hydrogel in the presence of a plurality of liposomes.
According to some of any of the embodiments of the present invention, forming the hydrogel is such that the liposomes are dispersed throughout the bulk of the hydrogel.
According to some of any of the embodiments of the present invention, the hydrogel or composite material containing a hydrogel features a dynamic shear storage modulus (G′) of at least 1000 Pa.
According to some of any of the embodiments of the present invention, the method is effected such that the dynamic friction coefficient in aqueous medium of the hydrogel or composite material containing a hydrogel having the liposomes dispersed therein ranges from 0.001 to 0.08 under a pressure of at least 1 atmosphere.
According to some of any of the embodiments of the present invention, the method is effected such that the dynamic friction coefficient in aqueous medium of the hydrogel or composite material containing a hydrogel having the liposomes dispersed therein is reduced by a factor of at least 52 relative to the friction coefficient of the hydrogel not having the liposomes dispersed therein.
According to some of any of the embodiments of the present invention, the method further comprises dehydrating the hydrogel or the composite material containing a hydrogel and rehydrating the hydrogel.
According to some of any of the embodiments of the present invention, the method, composite or composition presented herein comprises liposomes which are selected from the group consisting of small unilamellar vesicles (SUV), large unilamellar vesicles (LUV) and multilamellar vesicles (MLV).
According to some of any of the embodiments of the present invention, the liposomes comprise at least one phosphatidylcholine phospholipid.
According to some of any of the embodiments of the present invention, the liposomes comprise at least 50 molar percent of the phosphatidylcholine phospholipid.
According to some of any of the embodiments of the present invention, the water content of the hydrogel when fully hydrated ranges from 30% to 99% by weight of the total weight of the composition.
According to some of any of the embodiments of the present invention, the friction coefficient is substantially maintained at room temperature.
According to some of any of the embodiments of the present invention, the friction coefficient is substantially maintained at 37° C.
According to some of any of the embodiments of the present invention, the friction coefficient is substantially maintained over a period of at least 60 minutes under essentially constant load and temperature.
According to some of any of the embodiments of the present invention, the friction coefficient is substantially maintained after at least one dehydration-rehydration cycle.
According to an aspect of some embodiments of the present invention, there is provided an article-of-manufacturing which comprises the composition or composite material as described herein, in any one of the respective embodiments, and any combination thereof.
According to some embodiments, the article-of-manufacturing is selected from the group consisting of an implantable medical device, a drug-delivery system, a solid body, a disc, a fiber, a fabric, a tube, a film, a rod, a ring, a tubular mesh and any combination thereof.
According to an aspect of some embodiments of the present invention, there is provided a use of the article-of-manufacturing as described herein, in any of the respective embodiments, and any combination thereof, for an application selected from the group consisting of surface coating, friction-reduction, and a cutting tool coating.
According to an aspect of some embodiments of the present invention, there is provided a method of treating a living organism suffering from a medical condition associated with loss of, or damaged, cartilage, the method comprising replacing at least a portion of the cartilage with the composition or composite material as described herein, in any of the respective embodiments, and any combination thereof.
According to some embodiments, the composition described herein, in any of the respective embodiments, and any combination thereof is for use in replacing missing or damaged cartilage in a living organism suffering from a medical condition associated with loss of or damaged cartilage.
According to some embodiments, the composition as described herein, in any of the respective embodiments, and any combination thereof is for use in a skeletal joint replacement or reconstruction, vertebrate replacement or reconstruction, tendon replacement, tissue regeneration and reduction of tissue irritation by an implantable device.
According to an aspect of some embodiments of the present invention, there is provided a use of the composition as described herein, in any of the respective embodiments, and any combination thereof, for coating an article-of-manufacturing.
According to another aspect of embodiments of the present invention, there is provided a use of the composition as described herein, in any of the respective embodiments, and any combination thereof for lowering the friction coefficient of a surface under aqueous conditions.
Unless otherwise defined, all technical and/or scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which the invention pertains. Although methods and materials similar or equivalent to those described herein can be used in the practice or testing of embodiments of the invention, exemplary methods and/or materials are described below. In case of conflict, the patent specification, including definitions, will control. In addition, the materials, methods, and examples are illustrative only and are not intended to be necessarily limiting.
Some embodiments of the invention are herein described, by way of example only, with reference to the accompanying drawings. With specific reference now to the drawings in detail, it is stressed that the particulars shown are by way of example and for purposes of illustrative discussion of embodiments of the invention. In this regard, the description taken with the drawings makes apparent to those skilled in the art how embodiments of the invention may be practiced.
In the drawings:
The present invention, in some embodiments thereof, relates to material science, and more particularly, but not exclusively, to compositions and method for reducing the friction coefficient of hydrogels or of composite materials comprising a hydrogel, and to uses of such low friction hydrogels or composite materials containing same.
The principles and operation of some embodiments of the present invention may be better understood with reference to the figures and accompanying descriptions.
Before explaining at least one embodiment of the invention in detail, it is to be understood that the invention is not necessarily limited in its application to the details set forth in the following description or exemplified by the Examples. The invention is capable of other embodiments or of being practiced or carried out in various ways.
The present inventors have surprisingly uncovered that the incorporation of liposomes in the process of forming hydrogels, results in reduction of the friction coefficient of the hydrogel, compared to the friction coefficient of the equivalent hydrogel not having liposomes dispersed therein.
The present inventors have further identified some parameters of the hydrogel and/or the incorporated liposomes, which lead to enhanced reduction of the friction coefficient of the hydrogel.
As discussed hereinabove, while hydrogels may possess many qualities that render these materials suitable for various applications, such as cartilage replacement, or scaffolds for tissue engineering, their inherent friction coefficient is typically too high and degradation, delamination or other undesirable effects arising from high friction at the hydrogel surface, occur at a high rate and limit their efficiency. Thus, a hydrogel with reduced friction coefficient is of high interest.
As indicated hereinabove, incorporation of liposomes in hydrogels has been generally used heretofore in the context of a matrix, in the form of a hydrogel, for dispensing drug-delivery vehicles, in the form of liposomes, for various medical proposes. These hydrogels, dispensing liposomes for drug-delivery, are typically soft (Young's modulus or shear storage modulus (G′) of less than 1000 Pa) and lose their microscopic structure under mild loads.
While conceiving the present invention, the inventors have contemplated using hydrogels, or composite materials containing same, under high loads/pressures conditions, such as apply in skeletal joints. Hydrogels used in such applications should typically exhibit Young's modulus or shear storage modulus (G′) of no less than 1000 Pa, and, as discussed hereinabove, are limited by their high friction coefficient. To this end, the present inventors have recognized that reduction of the friction coefficient of the hydrogels is required for effective performance under such conditions and have designed and successfully practiced a methodology for reducing the hydrogel (or composite containing same) friction coefficient by incorporating liposomes within the hydrogel.
While reducing the present invention to practice, hydrogels which exhibit shear storage modulus (G′) of 1000 Pa of higher, such as HEMA hydrogels, were prepared while adding liposomes to the hydrogels prior to their curing stage, and were found to exhibit a notable shear reduction, or a notable reduction in their friction coefficient (μ). As demonstrated in the Examples section that follows, the effective friction coefficient measured under high load of 3000 grams for an exemplary poly(2-hydroxyethylmethacrylate) hydrogel crosslinked with 1% ethylene glycol dimethacrylate (referred to hereinbelow as HEMA EG 1%) was reduced by a factor of 30 from 0.2-0.25 to 0.01 when MLV HSPC liposomes at a stock concentration of 45 mM were added prior to the gelation process, both in experiments measuring friction of hydrogel versus hydrogel and in experiments measuring friction of the hydrogel against a round metal object. As further demonstrated in the Examples section that follows, this 30-fold reduction of the friction coefficient may be regarded as a lower bound value, as the neat HEMA hydrogel (not containing liposomes) could not withstand high pressures, and was crushed under high loads (in other words, the reduction in friction coefficient is even greater than the 30-fold indicated).
As further demonstrated in the Examples section that follows, the effective friction coefficient of the hydrogel measured under high loads of maximum of 8000 grams for an exemplary poly(2-hydroxyethylmethacrylate) crosslinked with 4% 9EGDMA (a polyethylene glycol dimethacrylate crosslinking agent having an average molecular weight of 550) (such hydrogel is referred to herein as HEMA 9EGDMA 4%) was reduced by a factor of at least 30 from 0.3 to 0.01 in the hydrogel against metal friction measurements, while the neat hydrogel crushed under such high loads.
While further contemplating various uses and applications of the compositions of the present embodiments, drying and rehydrating the hydrogels was attempted, and the results presented in the Examples section that follows show that the rehydrated liposome-incorporating hydrogels reduced the friction coefficient as efficiently as the liposome-incorporating hydrogels that had not been dehydrated.
The studies of various exemplary hydrogel/liposomes compositions as presented herein led to the identification of several factors which govern the capacity to reduce the friction coefficient of a hydrogel by incorporating liposomes therein. These factors include, without limitation:
In some of the present embodiments, maximal reduction of the friction coefficient of any given hydrogel can be afforded by selecting optimal values for one or more of the above factors. It is noted herein that for practical considerations, the hydrogel component of the hydrogel/liposomes composition presented herein, should exhibit some capacity to withstand at least some load or force, namely be characterized by a certain degree of “hardness”, which can be expressed by a shear storage modulus (G′) of at least 1000 Pa.
According to an aspect of embodiments of the present invention, there is provided a composition which includes a hydrogel and a plurality of liposomes incorporated in the hydrogel, wherein the composition is characterized by a shear storage modulus (G′) of at least 1000 Pa.
In some embodiments, the liposomes are dispersed throughout the bulk of the hydrogel. In some embodiments, forming the hydrogel in the presence of liposomes results in dispersion of the liposomes within the bulk of the hydrogel.
Hydrogels:
As used herein, the term “hydrogel” refers to a three-dimensional fibrous network containing from about 50%, or from about 80%, and up to 99.9% (by mass) water. A hydrogel can be regarded as a material which is mostly water, yet behaves like a solid or semi-solid due to a three-dimensional crosslinked network within the liquid, made of natural and/or synthetic polymeric chains. According to some embodiments of the present invention, a hydrogel may contain polymeric chains of various lengths and chemical compositions which may stem from monomers, oligomers, block-polymeric units, which are inter-connected (crosslinked) by chemical bonds (covalent, hydrogen and ionic/complex/metallic bonds).
A hydrogel, according to some embodiments of the present invention, may contain macromolecular polymeric and/or fibrous elements which are not chemically connected to the main crosslinked network but are rather mechanically intertwined therewith and/or immersed therein. Such macromolecular fibrous elements can be woven (as in, for example, a mesh structure), or non-woven, and can, in some embodiments, serve as reinforcing materials of the hydrogel's fibrous network. Non-limiting examples of such macromolecules include polycaprolactone, gelatin, gelatin methacrylate, alginate, alginate methacrylate, chitosan, chitosan methacrylate, glycol chitosan, glycol chitosan methacrylate, hyaluronic acid (HA), HA methacrylate, and other non-crosslinked natural or synthetic polymeric chains and the likes. According to some of any of the embodiment of the present invention, the amount of such non-crosslinked additives is small and typically does not exceed 100 mg in 1 ml of the hydrogel-forming precursor solution.
In the context of embodiments of the present invention, when a hydrogel is used in combination with such macromolecular structures, it is referred to interchangeably as “a composite material comprising a hydrogel”, “a composite structure comprising a hydrogel”, “hydrogel-containing composite material or structure”, “hydrogel-containing composite” or simply as “a hydrogel” or as a “composite”. Thus, the term “hydrogel” is meant to encompass hydrogel/fiber-network composites wherein a network of intertwined and/or woven fibers is engulfed in a mass of a hydrogel. In general, a composite material comprising a hydrogel may further comprise a woven mesh of fibers, non-woven fibers, a plurality of rods, a net etc. Exemplary hydrogel/fiber-network composites are described, for example, in Moutos et al. Nat. Mater., 2007, 6(2), p. 162-7.
According to some embodiments of the present invention, the hydrogel may contain additional elements which render it useful for specific applications, such as therapeutic and labeling agents, as these are discussed below, scaffold and other structural elements, live cells, cellular components and the like.
Hydrogels may take a physical form that ranges from soft, brittle and weak to hard, elastic and tough material. Soft hydrogels may be characterized by rheological parameters including elastic and viscoelastic parameters, while hard hydrogels are more suitably characterized by tensile strength parameters, elastic, storage and loss moduli, as these terms are known in the art.
The softness/hardness of a hydrogel is governed inter alia by the chemical composition of the polymer chains, the “degree of crosslinking” (number of interconnected links between the chains), the aqueous media content and composition, and temperature. In some embodiments, the hydrogel is reinforced with other fibrous material to form a composite structure, which exhibits high tensile strength compared to a neat hydrogel, as discussed hereinabove for a composite material containing a hydrogel. In some embodiments of the present invention, the hardness of the neat hydrogel is similar to the hardness of the hydrogel/liposomes compositions, meaning that the inclusion of liposomes in the bulk of the hydrogel does not affect the hardness values significantly, or lower/augment it mildly. It is noted herein that since the inclusion of liposomes reduces the friction coefficient of the hydrogel, the hydrogel is able to sustain the loads and forces applied thereon during the measurements of tensile moduli, hence in some cases the tensile strength expressed in storage modulus G′ appears to change from neat to liposome incorporation.
In some cases, the ability to form crosslinks between the polymeric chains during the curing of a hydrogel, is an intrinsic property of the hydrogel-forming agent, namely the hydrogel-forming agent exhibits “crosslinkable functional groups” that can form bonds therebetween under certain conditions (initiation or activation), thereby form crosslinking bonds between the polymers making the hydrogel. Crosslinkable functional groups can be introduced into a polymeric chain by including a certain amount of certain crosslinkable monomers in the total amount of monomers that form the polymeric chain, wherein those crosslinkable monomers are characterized by having at least three functionalities, at least one of these is a crosslinkable functional group which can form bonds with other crosslinkable functional groups on other polymeric chains during or after the polymerization process. In such an example, a growing polymeric chain will exhibit a crosslinkable functional group along its chain at a certain frequency that corresponds to the relative concentration of the crosslinkable monomer in the pre-polymerization formulation (percentage).
Exemplary crosslinkable monomers include, without limitation, the family of di- and triacrylates monomers, which have three polymerizable functionalities, one of which can be regarded as a crosslinkable functional group. Diacrylates monomers include, without limitation, methylene diacrylate, and the family of poly(ethylene glycol). dimethacrylate (nEGDMA), Triacrylates monomers include, without limitation, trimethylolpropane triacrylate, pentaerythritol triacrylate, tris (2-hydroxy ethyl) isocyanurate triacrylate, isocyanuric acid tris(2-acryloyloxyethyl) ester, ethoxylated trimethylolpropane triacrylate, pentaerythrityl triacrylate and glycerol triacrylate, phosphinylidynetris(oxyethylene) triacrylate.
In another example, certain functional groups present at a certain frequency in a pre-formed polymer, can be converted into crosslinkable functional groups by a variety of chemical modifications. For example, an amino group of a side-chain in a polymer, such as a polypeptide, can be converted into a crosslinkable functional group by coupling the amino group with an acrylate to thereby form an acrylate functional group along the polymeric chain that can form crosslinks with similar acrylate functionalities on other polymeric chains.
In the context of some embodiments of the present invention, since a crosslinking agent per-se is not used in the crosslinking (curing) process of hydrogel-forming agents having crosslinkable functional groups incorporated therein, the number of such crosslinkable functional groups, relative to the total number of monomers in the hydrogel-forming agent, can be correlated to the degree of crosslinking in such hydrogels.
For example, in the case of gelatin methacrylate, the degree of methacrylation can be correlated to the degree of crosslinking, considering that 3.5% of the polymeric units (monomers) of gelatin can potentially undergo methacrylation (the frequency of the crosslinkable monomers within the polymer), that only a certain percent of these units (crosslinkable monomers) actually undergo methacrylation, and that each two methacrylated units form a single crosslinking bridge. In one example, if 75% of these units undergo methacrylation, and every two methacrylic moieties form one crosslinking bond, the molar percent of a crosslinking agent to hydrogel-forming agent in the case of gelatin methacrylate-based hydrogels is about 3.5%*0.75/2=1.3%. A similar calculation applies to other hydrogel-forming agents having crosslinkable functional groups as part of their chemical structure.
As the hardness of the hydrogel is correlated to the degree of crosslinking, one way to signify the hydrogel hardness is by denoting the amount of the crosslinking agent used in its preparation. Ultimately, hydrogels' hardness is measured by standard elastic, storage and loss moduli.
According to some of any of the embodiments of the present invention, the hydrogel/liposomes compositions presented herein are based on a hydrogel which is characterized by a storage modulus is 1000 Pa or higher in its neat form (without liposomes and/or additional components which form a composite as described herein). In some embodiments, the storage modulus of the hydrogel without liposomes is greater than 2000 Pa, greater than 3000 Pa, greater than 4000 Pa, greater than 5000 Pa, greater than 7 KPa, greater than 10 KPa or greater than 20 KPa.
According to some of any of the embodiments of the present invention, the hydrogel/liposomes compositions presented herein are based on a hydrogel-containing composite which is characterized by a storage modulus higher than 1000 Pa (without liposomes). In some embodiments, the storage modulus of the hydrogel-containing composite without liposomes is greater than 2000 Pa, greater than 3000 Pa, greater than 4000 Pa, greater than 5000 Pa, greater than 7 KPa, greater than 10 KPa or greater than 20 KPa.
As can be appreciated, these hydrogels or composite materials containing same are capable of preserving their structural integrity under considerable loads, while softer hydrogels tear and squeeze out under similar loads.
Hydrogels are formed from hydrogel-forming agents in the presence of a crosslinking agent and other optional components. Hence, according to embodiments of the present invention, a hydrogel may be defined by its chemical composition, namely the type of the hydrogel-forming agent and the type (and amount) of the crosslinking agent.
Hydrogel-forming agents include, for example, polymerizable monomers, a mixture of different polymerizable monomers, a mixture of monomers, oligomers, block polymers, short and long polymeric chains (polymers) and any combination thereof.
Non-limiting examples of hydrogel-forming agents, which can be used in some of any the embodiment of the present invention, include hydroxyethyl methacrylate (HEMA), hydroxyethyl acrylate (HEA), acrylamide (AAm), methacrylamide (MAAm), acrylic acid (AAc), methacrylic acid (MAAc), hydroxyethyl acrylate (HEA), hexyl methacrylate, N-isopropylacrylamide (NiPAAm)), N-isopropylmethacrylamide, polylactic acid, polyamide, polyethylene-terephthalate (PET), polyvinyl alcohol, polyurethane, polycaprolactone, polyethylene glycol (also known as polyethylene oxide, PEG or PEO), N,N-dimethacrylamide (nnDMAA), hyaluronic acid (HA), HA methacrylate, polycaprolactone, peptides, saccharides, gelatin, gelatin methacrylate, chitosan, chitosan methacrylate, glycol chitosan, glycol chitosan methacrylate,alginate, alginate methacrylate, cellulose, siloxanes, polysiloxanes, and any oligomer and polymer thereof, in any combination thereof.
According to some embodiments of the present invention, the water content of a fully hydrated hydrogel ranges from 50% to 99.9%, or from 70% to 99.9%, or from 80% to 99.9%, or from 90 to 99.9%, or from 90 to 99%, including any range or value therebetween, by weight of the total weight of the hydrogel/liposomes composition presented herein.
Crosslinking:
When the term “crosslinking” is used in the context of hydrogels, it usually refers to the use of crosslinking agents, as defined herein, to promote a difference in the polymer composition's physical properties. The “degree of crosslinking” can be correlated to mechanical parameters which can be measured by several experimental methods, including modulus and swelling measurements. These measurements can correlate the “molar percent of a crosslinking agent to hydrogel-forming agent” to various chemical and mechanical parameters that characterize a hydrogel. These parameters include, for example, the degree of swelling, the polymer volume fraction in the hydrogel, the crosslink density (mol/cm3), the network chain density (mol/cm3) and the network chain molecular weight (gram/mol).
As used herein, the phrase “crosslinking agent” refers to a substance that promotes or regulates intermolecular covalent, ionic, hydrogen or other form of bonding between polymeric chains, linking them together to create a network of polymeric chains which result in increasing the rigidity of the structure. Crosslinking agents typically exhibit one or more, preferably two or more, bonding functionalities, for example, two double (vinyl) bonds (a functionality of four, or tetrafunctionality), three amines (a functionality of three, or trifunctionality), creating chemical bonds between two or more polymer chains.
Comonomers constitute a type of crosslinking agents which are contemplated in some embodiments of the present invention. A comonomer is a monomer having at least three bonding functionalities (trifunctionality), which is incorporated into the backbone of a growing polymer in the course of the polymerization/gelation process. While two of its functionalities are used to form the polymeric backbone, the third (and more) functionality is free to form crosslinks with counterparts in other polymeric chains. In general, comonomers are used to generate crosslinking homogeneously along the polymeric chain. It is noted herein that the term “comonomer” is meant to encompass oligomers and short polymers, having at least three bonding functionalities, which can be incorporated into a growing polymer during the polymerization process.
In general, the crosslinking agent is selected according to the chemistry and polymerizing conditions used to form the polymeric backbone of the hydrogel. Non-limiting examples of crosslinking agents, according to some embodiments of the present invention, include ethylene glycol dimethylacrylate (EGDMA), poly(ethylene glycol) dimethacrylate (also known as polyethyleneoxide dimethacrylate, poly-EGDMA, nEGDMA or PEOdMA), N,N′ -methylenebisacrylamide (MBA or MBAm), N,N′-methylenebis(2-methylacrylamide), methylene diacrylate, methylene bis(2-methylacrylate), diethylene glycol diacrylate, hexamethylene diacrylate, oxybis(methylene) bis(2-methylacrylate), oxybis(ethane-2,1-diyl) bis(2-methylacrylate), and glutaraldehyde.
As discussed hereinabove, the degree of crosslinking of a hydrogel can be expressed in terms of the amount of crosslinking agent used in the making thereof. This value is typically given in molar percent of a crosslinking agent to hydrogel-forming agent(s). This value corresponds roughly with the number of crosslinks per polymer chain length, as each crosslinking agent residue forms one crosslink in the network. Determining this value is based on the percentage of the molar content of the crosslinking agent(s) to the molar content of all hydrogel-forming agents which form chemical bonds that are part of the polymeric chains that make the hydrogel network.
In some embodiments wherein the hydrogel-forming agent exhibits crosslinkable functional groups which form the crosslinking bonds directly therebetween without a crosslinking agent per-se, the number of these crosslinkable functional groups is related to the amount of crosslinking agent such that two crosslinkable functional groups are counted as one crosslinking agent molecule. In terms of molar content and relative percentage, the value given for the degree of crosslinking is therefore half of the frequency of the monomers exhibiting crosslinkable functional groups out of the total number of monomers in the hydrogel-forming agent.
Other molecules that may form other type of non-chemical interactions, such as entanglement, are not taken into account. For example EGDMA 1% means 0.01 mol of EGDMA to every 1 mol of HEMA monomers.
Thus, the hydrogel component of the hydrogel/liposomes composition, according to some embodiments of the present invention, can be characterized by the molar percent of the crosslinking agent used in its preparation, a measure that typically correlates with the degree of crosslinking. In the context of some embodiment of the present invention, the degree of crosslinking is defined as the molar ratio in percents, or molar percentage, of the crosslinking agent relative to the hydrogel-forming agent(s). In other words, in cases where the molar amount of hydrogel-forming agent is 100 and the molar amount of the crosslinking agent is 2, the degree of crosslinking is 2%. According to some of any of the embodiments of the present invention, the molar percentage of the crosslinking agent ranges from 0.00001% to 50% per hydrogel-forming agent's total molar content. In some embodiments, the range of molar percentage of the crosslinking agent ranges from 0.01% to 25%, from 0.2% to 25%, from 1% to 20% or from 1% to 15%, including any subranges and intermediate values therebetween.
According to some of any of the embodiments described herein, various ranges and subranges of the molar percentage of the crosslinking agent are used in combination with various hydrogels, various liposome sizes, various liposome concentrations, and various other parameters, as these are defined herein, and embodiments of the present invention encompass all of such combination. In some embodiments, the degree of crosslinking is selected according to a the hydrogel type, liposome size, liposome concentration and/or other parameters, in various combinations, to maximize the capacity to reduce the friction coefficient of any given hydrogel by incorporating liposomes therein.
As demonstrated in the Examples section that follows, the molar percent of the crosslinking agent correlates to the size and concentration of the liposomes, namely there are specific combinations of these parameters (hydrogel crosslinking, liposome size and liposome concentration) that confer a greater reduction in friction coefficient than other combinations. For example, one sub-range of crosslinking of 0.00001% to 0.2% may correspond to liposomes having an average diameter (D) of more than 100 nm, while another sub-range of crosslinking of 0.21% to 25% may correspond to liposomes having D larger than 80 nm and a concentration 5 mM or higher.
In some of embodiments of the present invention, as described hereinbelow, the degree of crosslinking of the hydrogel is 0.2 molar percent or higher.
In some embodiments of the present invention, as described hereinbelow, the degree of crosslinking of the hydrogel is 0.2 molar percent or lower.
Liposomes:
Pristine hydrogels not having liposomes incorporated therein, also referred to herein as “neat” hydrogels, typically have a friction coefficient (μ) in aqueous conditions in the range of 0.5-1 (e.g., for HEMA-based hydrogels). These values indicate that neat hydrogels, used under some load in an aqueous environment, are not suitable for applications requiring much lower friction under load. When liposomes are incorporated therein, according to the present embodiments, these values of the friction coefficient drop down by a factor of up to 60 and even more.
In the context of some embodiments of the present invention, liposomes are artificial vesicles composed of a substantially spherical lipid bilayer which typically comprises phospholipids, cholesterol and other lipids. Main liposome types include small unilamellar vesicles (SUV) which typically exhibit an average diameter under 100 nm, large unilamellar vesicle (LUV) which typically exhibit an average diameter larger than 100 nm, and multilamellar vesicle (MLV) which typically exhibit an average diameter that may range from about 80 or about 100 nm to 1 μm and larger. In the context of some embodiments of the present invention, SUV liposomes have an average diameter of 80 nm or lower, and MLV liposomes have an average diameter higher than 80 nm.
It is noted that the use of liposome aqueous suspensions as lubricants is not equivalent to lowering the friction coefficient of a hydrogel by incorporating liposomes therein, since a hydrogel having a low friction coefficient may not need lubrication; namely a lubricant is not equivalent to a material having a low friction coefficient. Without being bound by any particular theory, it is noted herein that the use of liposomes dispersed in a hydrogel rather than the use of liposome in liquid suspension applied to the surface of a hydrogel, is advantageous, as it provides a reservoir of liposomes within the hydrogel that result in a self-healing action when wear occurs at the hydrogel surface. Thus, for example, a low friction coefficient of the hydrogel is maintained for extended periods while the liposomes applied from dispersion on a hydrogel's surface may lose their friction reduction property as soon as the dispersion is removed.
Without being bound to any particular theory, it is suggested that the micro-structural effect of incorporation of liposomes in a hydrogel can result in the distribution of the liposomes throughout the bulk of the hydrogel, or in other words, results in dispersion of liposomes in the hydrogel.
In some embodiments of the present invention, the liposomes are distributed in the hydrogel substantially uniformly in a single liposome form or in the form of clusters of liposomes, as seen in exemplary hydrogel/liposomes compositions and presented in the Examples section that follows (see,
It is noted that in general, liposomes having a small diameter have a high radius of curvature that confers an asymmetric distribution of the bilayer constituents. Furthermore, small liposomes are limited in terms of the encapsulation of aqueous space per mole of lipid. Hence, liposomes having a small diameter may exhibit a less stable spherical structure. Relatively unstable liposomes May be disadvantageous, especially while applying high loads and shearing the hydrogel with its liposome composition, or may be advantageous, in embodiments where liposome breakdown is desirable.
According to some of any of the embodiments of the present invention, the liposomes dispersed throughout the bulk of the hydrogel are greater than 80 nm in diameter. Alternatively, the liposomes dispersed throughout the bulk of the hydrogel, according to some embodiments of the present invention, are greater than 20 nm, greater than 30 nm, greater than 40 nm, greater than 50 nm, greater than 60 nm, greater than 70 nm, greater than 80 nm, greater than 90 nm, greater than 100 nm, greater than 150 nm, greater than 200 nm, greater than 250 nm, greater than 300 nm, greater than 400 nm, greater than 500 nm, greater than 600 nm, greater than 700 nm or greater than 900 nm in diameter.
It is noted herein that liposomes are prone to swelling and growth, and also tend to form aggregates, change from SUV to MLV and form cochleates and other super-structures such as bicontinuous structures. This instability, mostly observed in SUV of diameters smaller than 80 nm, should be considered when designing a hydrogel encapsulating the same. Liposomes of 80 nm in diameter or less may require stabilization which may be achieved with the use of various agents, as described hereinafter. Liposomes of 80 nm in diameter or less may be practical for use in some embodiments of the present invention, under certain stabilizing conditions and s hydrogel parameters, to lower the friction coefficient of hydrogels.
The size of the liposomes stated herein and throughout refers to the size which has been measured shortly before gelation and incorporation of the liposomes in the hydrogel's network. It is also noted that comparing the light scattering size of the liposomes prior to incorporation in the hydrogels with electron-microscopy measurements using fracture techniques indicates that the liposomes do not change their size once entrapped in the hydrogel's network.
Phosphatidylcholines constitute a class of phospholipids that incorporate phosphocholine as a head-group. Without being bound by any particular theory, it is assumed that the phosphocholine moiety confers the high hydration state of liposomes which directly or indirectly affect the capacity to lubricate surfaces and lower the friction coefficient of the hydrogels/liposomes compositions presented herein.
According to some of any of the embodiment of the preset invention, the liposomes that are incorporated into hydrogels are comprised of at least one phosphatidylcholine phospholipid. According to some embodiment of the preset invention, the liposomes are composed of at least 50 molar percent phosphatidylcholine phospholipids out of the total lipid composition of the liposome. In some embodiments, the phosphatidylcholine phospholipid content in the liposomes is 20 molar percent, at least, at least 30 molar percent, at least 40 molar percent, at least 60 molar percent, at least 70 molar percent, at least 80 molar percent, at least 90 molar percent, or 100 molar percent of the total lipid composition of the liposome. In some embodiments, the phospholipid consists essentially of at least one phosphatidylcholine.
In some embodiments of any one of the embodiments described herein, the amphiphilic lipid described herein (e.g., in liposomes described herein) is characterized by a molar percentage of phosphatidylcholine (the at least one phosphatidylcholine described herein) in the total amount of lipids making the liposome, which is at least 20%. In some embodiments, the molar percentage is at least 40%. In some embodiments, the molar percentage is at least 50%. In some embodiments, the molar percentage is at least 60%. In some embodiments, the molar percentage is at least 70%. In some embodiments, the molar percentage is at least 80%. In some embodiments, the molar percentage is at least 90%. In some embodiments, the amphiphilic lipid consists essentially of at least one phosphatidylcholine.
The fatty acyl groups in a lipid described herein may comprise saturated fatty acyl groups, monounsaturated fatty acyl groups (having a single unsaturated bond) and/or polyunsaturated fatty acyl groups (having two or more unsaturated bonds). In some embodiments, the unsaturated bonds are cis double bonds.
Examples of suitable saturated fatty acyl groups include, without limitation, lauroyl, myristoyl, palmitoyl and stearoyl.
Examples of suitable monounsaturated fatty acyl groups include, without limitation, oleoyl, palmitoleoyl, eicosenoyl, erucoyl, nervonoyl and vaccenoyl.
Examples of suitable polyunsaturated fatty acyl groups include, without limitation, linoleoyl, α-linolenoyl, γ-linolenoyl, dihomo-γ-linolenoyl, stearidonoyl, eicosatetraenoyl, eicosapentaenoyl, docosapentaenoyl, docosahexaenoyl, arachidonoyl and adrenoyl.
In some embodiments of any one of the embodiments described herein, the fatty acyl groups are selected from the group consisting of saturated and monounsaturated fatty acyl groups. In some embodiments, the fatty acyl groups are saturated fatty acyl groups.
Without being bound by any particular theory, it is believed that saturated and monounsaturated fatty acyl groups, particularly saturated fatty acyl groups, are relatively resistant to chemical reaction such as oxidation, and therefore provide a more resilient system.
In some embodiments of any one of the embodiments described herein, at least 50% of the fatty acyl groups are the same species of fatty acyl group (e.g., myristoyl, palmitoyl). In some embodiments, at least 75% of the fatty acyl groups are the same species of fatty acyl group. In some embodiments, at least 90% of the fatty acyl groups are the same species of fatty acyl group.
Exemplary phospholipids comprising a single species of fatty acyl group include 1,2-dimyristoyl-sn-glycero-3-phosphocholine and 1,2-dipalmitoyl-sn-glycero-3-phosphocholine.
According to some of any embodiment of the present invention, the phosphatidylcholine is selected from the group consisting of 1,2-dilauroyl-sn-glycero-3-phosphocholine (DLPC), 1,2-dimyristoyl-sn-glycero-3-phosphocholine (DMPC), 1,2-dipalmitoyl-sn-glycero-3-phosphocholine (DPPC), hydrogenated soybean phosphocholine (HSPC) and 1,2-distearoyl-sn-glycero-3-phosphocholine (DSPC), and any combination thereof.
According to embodiments of the present invention, the concentration of the liposomes in the hydrogel-forming composition is at least 1 mM, at least 2 mM, at least 4 mM, at least 6 mM, at least 10 mM, at least 12 mM, at least 16 mM, at least 20 mM, at least 24 mM, at least 30 mM, at least 35 mM, at least 40 mM, at least 60 mM, at least 100 mM or at least 200 mM, including any intermediate values and including any subranges within 1 mM to 200 mM. Higher concentrations are also contemplated.
According to some embodiments of the present invention, the concentration of the liposomes in the hydrogel-forming composition is higher than 4 mM, or is 4 mM or lower, depending on other various parameters of the hydrogel, as described in further detail hereinunder.
According to some of any of the embodiments of the present invention, the liposomes encapsulate or incorporate into their lipid bilayer, or, are used in combination with, an additional active agent. The additional agent can be used in the preparation of the liposomes, and such additional agents, in some embodiments, can be a polymer, cholesterol, a liposome-stabilizing agent and/or an active agent, while an active agent can be a labeling agent, a bioactive agent or a therapeutically active agent. In some cases, the additional agent can serve one, two or all three of the above functions.
Liposomes can be prepared such that the lipid bilayer comprises stabilizing components, surface-altering components and structure-altering components. Furthermore, liposomes can encapsulate various factors, solutes, compounds, macromolecules, viral components, viruses, genetic-coding materials, drugs and many other chemical entities. Such chemical entities, whether incorporated into the lipid bilayer or encapsulated within the liposome, may affect the structure of the liposome in terms of its size and stability, may affect the reactivity of the liposome towards other chemical entries, and affect its capacity to lower the friction coefficient of a hydrogel in-which it is dispersed.
As observed by the present inventors, adding liposome-stabilizing agents, such as cholesterol, glucosamine, polycaprolactone, dextrose and other sugars, or polymers such as hyaluronan (hyaluronic acid or hyaluronate or HA), chitosan, chitosan methacrylate, glycol chitosan, glycol chitosan methacrylate, or alginate to the preparation of the liposomes, allows the hydrogel/liposomes compositions presented herein to sustain the low friction coefficient under larger loads compared to similar compositions wherein the liposomes did not contain the stabilizing component. It is noted that adding polymers which are not part of the crosslinked network of the hydrogel, can be effected at the liposome preparation process or at the hydrogel solution preparation process, prior to initiation of the crosslinking process and the curing step.
According to some of any of the embodiment of the present invention, the liposomes which are incorporated (encapsulated) in the hydrogel, are prepared in the presence of a polymer, a hydrogel-forming polymer and/or liposome-stabilizing agent. In some of these embodiments, the additional agent is a polymer, as described hereinabove. Non-limiting examples of polymers which can be used in this context of the present invention, include polycaprolactone, poly(2-hydroxyethyl methacrylate) (pHEMA), alginate and hyaluronic acid (HA). In some embodiments, the concentration of the liposome-stabilizing polymer in the liposome preparation solution ranges from 0.1 mg polymer per 1 ml of liposome suspension solution to 5 mg/ml.
According to some of any of the embodiment of the present invention, the liposomes which are incorporated (encapsulated) in the hydrogel, are prepared while including cholesterol in the lipid formulation of the liposomes. In some embodiments, the concentration of cholesterol in the liposome preparation solution ranges from 1% (molar percent) to 50%, relative to the total amount of lipids in the liposome preparation solution. In some embodiments, the concentration of cholesterol ranges from 1% to 40%, 1% to 30%, 1% to 20%, 1% to 15%, 1% to 10% or 1% to 5% and all the possible subranges as well as individual numerical values within that range. According to some embodiments of any embodiment of the present invention, the concentration of cholesterol ranges from 1% to 10% (molar percents). In some embodiments, the concentration of cholesterol in the liposome is lower than 50% (molar percents).
The liposomes in the hydrogel/liposomes compositions presented herein may also be used as drug-delivery vehicles, as this concept is known in the art. According to some of any of the embodiments of the present invention, the liposomes as described herein encapsulate at least one additional active agent such as a labeling agent, a therapeutically active agent and/or bioactive agent, as these terms are defined herein.
The encapsulation or the incorporation into the bilayer of an additional active agent in the liposomes dispersed in the compositions of the present embodiments can provide a dual utility for the composition. For example, when the composition is utilized in an implantable device such as a joint replacement device, the additional active agent may be a labeling agent, and the gradual release thereof to the biologic environment where the device is implanted can assist in diagnosing the function of the device. Alternatively, the additional active agent is a therapeutically active agent that can be beneficially released into the environment, thereby enhancing the function of the device as a drug-delivery device. Additional description of some of these embodiments is provided hereinunder.
As used herein, the phrase “a therapeutically active agent” describes a chemical substance, which exhibit a therapeutic activity when administered to a subject.
As used herein, the phrase “biologically active agent”, or “bioactive agent”, describes a chemical substance, which exhibits a biological or physiological activity in an organism.
As used herein, the phrase “labeling agent” refers to a detectable moiety or a probe and includes, for example, chromophores, fluorescent compounds, phosphorescent compounds, heavy metal clusters, and radioactive labeling compounds, as well as any other known detectable moieties.
Non-limiting examples of therapeutically active agents that can be beneficially used in embodiments of the present invention include, without limitation, one or more of an agonist agent, an amino acid agent, an analgesic agent, an antagonist agent, an antibiotic agent, an antibody agent, an antidepressant agent, an antigen agent, an anti-histamine agent, an anti-hypertensive agent, an anti-inflammatory drug, an anti-metabolic agent, an antimicrobial agent, an antioxidant agent, an anti-proliferative drug, an antisense agent, a chemotherapeutic drug, a co-factor, a cytokine, a drug, an enzyme, a growth factor, a heparin, a hormone, an immunoglobulin, an inhibitor, a ligand, a nucleic acid, an oligonucleotide, a peptide, a phospholipid, a prostaglandin, a protein, a toxin, a vitamin and any combination thereof.
The combined friction reduction and therapeutic effect is particularly advantageous when the hydrogel/liposomes composition is used in an application that also requires a localized enhanced effect of a therapeutically active agent, such as antimicrobial control, cell/tissue growth, regeneration and necrosis, vasodilatation/vasoconstriction, immunosuppression/immune-enhancement and the likes. Additional description of some of these embodiments is provided hereinunder.
In some of any of the embodiments of the present invention, the therapeutic agent also may comprise a vasodilator to counteract vasospasm, for example an antispasmodic agent such as papaverine. The therapeutic agent may be a vasoactive agent, generally such as calcium antagonists, or alpha and beta adrenergic agonists or antagonists. In some of any of the embodiments of the present invention, the therapeutic agent may include a biological adhesive such as medical grade cyanoacrylate adhesive or fibrin glue, the latter being used to, for example, adhere an occluding flap of tissue in a coronary artery to the wall, or for a similar purpose.
In some of any of the embodiments of the present invention, the therapeutic agent may be an antibiotic agent that may be released from the hydrogel, optionally in conjunction with a controlled release carrier for persistence, to an infected organ or tissue or any other source of localized infection within the body. Similarly, the therapeutic agent may comprise steroids for the purpose of suppressing inflammation or for other reasons in a bodily site. Exemplary anti-infective agents include, for example, chlorhexidine which is added for improved biocompatibility of articles-of-manufacturing comprising the hydrogels according to some of any of the embodiments of the present invention.
Friction Coefficient of Hydrogel/Liposomes Compositions:
As demonstrated in the Examples section below, incorporation of liposomes into the bulk of hydrogels affords hydrogels which are characterized by a dynamic friction coefficient in aqueous media that ranges from 0.001 to 0.08 under a pressure of at least 1 atmosphere. These values are not only low in comparison to neat hydrogels, but are notably low in absolute terms even in comparison to lubricated systems in aqueous media.
Unless stated otherwise, the friction coefficient values presented in the Examples section that follows below and referred to hereinthroughout, refer to dynamic friction coefficient, however, the general propensity to lower the friction coefficient of hydrogels is evident in both static and dynamic friction coefficients.
In some embodiments of the present invention, the friction coefficient of a hydrogel/liposomes composition, is at least 2-fold lower or at least 3-fold lower than the friction coefficient of the corresponding neat hydrogel, or at least 5-fold lower, at least 6-fold lower, at least 7-fold lower, at least 8-fold lower, at least 9-fold lower, at least 10-fold lower, at least 12-fold lower, at least 14-fold lower, at least 16-fold lower, at least 18-fold lower, at least 20-fold lower, at least 25-fold lower, at least 30-fold lower, at least 35-fold lower, at least 40-fold lower, at least 50-fold lower, or at least 60-fold or more lower than the friction coefficient of the corresponding neat hydrogel.
As presented in the Examples section below, it has been demonstrated that certain combinations of the size of the liposomes, concentration of the liposomes and the degree of crosslinking of the hydrogel, stand as conferring an highly efficient reduction in the friction coefficient of the composition compared to the neat hydrogel.
Small liposomes, according to embodiments of the present invention, are liposomes of less than 80 nm in diameter. Accordingly, large liposomes have a diameter larger than 80 nm.
According to embodiments of the present invention, a degree of crosslinking lower than 0.2% is regarded as a low degree of crosslinking (low crosslinking), while a degree of crosslinking larger than 0.2% is regarded as a high degree of crosslinking (high crosslinking).
A liposome concentration 4 mM or lower is regarded as a low concentration, according to embodiments of the present invention, while a high concentration of liposomes is higher than 4 mM.
Each of the combinations i-viii can be represented by specific parameters. Following are a few examples: The composition presented herein may be characterized by an average diameter of liposomes larger than 80 nm and/or a degree of crosslinking higher than 0.2 molar percent, and a concentration of liposomes higher than 4 mM. The composition presented herein may be characterized by an average diameter of liposomes larger than 80 nm, and a degree of crosslinking higher than 0.2 molar percent. The composition presented herein may be characterized by an average diameter of liposomes larger than 80 nm, and a degree of crosslinking 0.2 molar percent or lower. The composition presented herein may be characterized by an average diameter of liposomes larger than 80 nm, a degree of crosslinking higher than 0.2 molar percent, and a concentration of liposomes higher than 4 mM. The composition presented herein may be characterized by an average diameter of liposomes larger than 80 nm, a degree of crosslinking 0.2 molar percent or lower, and a concentration of liposomes higher than 4 mM. The composition presented herein may be characterized by an average diameter of liposomes larger than 80 nm, a degree of crosslinking higher than 0.2 molar percent, and a concentration of liposomes 4 mM or lower. The composition presented herein may be characterized by an average diameter of liposomes larger than 80 nm, a degree of crosslinking of 0.2 molar percent or lower, and a concentration of liposomes of 4 mM or lower.
In some embodiments, the low friction coefficient of the hydrogel/liposomes compositions presented herein is maintained under a wide range of loads and in various surface-to-surface combinations, including a gel-to-gel configuration and a gel-to-metal configuration, as these are described in detail in the Examples section hereinbelow.
For example, in a gel-to-gel configuration, wherein the hydrogel/liposomes compositions sample is a round shape having a diameter of about 6 mm, a load of about 300 grams corresponds to 1 atmosphere pressure pushing the samples towards one-another. In a gel-to-metal configuration, 1 atmosphere corresponds to a load of about 100 grams pushing a round metal head having a radius of 28 mm into the hydrogel surface.
The reduction in friction coefficient and the durability of these compositions under continuous sliding motion under loads is maintained at various temperatures and for extended duration of time. In some embodiments, the friction coefficient of the hydrogel/liposomes compositions presented herein, is substantially maintained at room temperature (e.g., 25° C.). In some embodiments, the friction coefficient of the hydrogel/liposomes compositions presented herein, is substantially maintained at a physiological temperature (e.g., 37° C.). In some embodiments, the friction coefficient of the hydrogel/liposomes compositions presented herein, is substantially maintained at room temperature as well as at 37° C. In some embodiments, the friction coefficient of the hydrogel/liposomes compositions presented herein, is maintained for at least 300 cycles while experiencing an essentially constant motion under load at room temperature and/or at 37° C.
The reduction in friction coefficient is maintained even after the hydrogel/liposomes composition has been dehydrated. This observation, discussed and presented in the Examples section below, is non-trivial for several reasons, including the fact that liposomes are known to lose integrity once dried, and therefore it would have been expected that the capacity to lower the friction coefficient would be lost once dehydrated. Nonetheless, dehydrated hydrogel/liposomes compositions regained their low friction coefficients once rehydrated. Thus, according to some embodiments of the present invention, the low friction coefficient of the hydrogel/liposomes compositions presented herein, is substantially maintained after at least one dehydration-rehydration cycle.
Method of Lowering the Friction Coefficient of a Hydrogel:
According to another aspect of some embodiments of the present invention, there is provided a method of lowering the friction coefficient of any given hydrogel, as this term is defined and exemplified hereinabove, which is effected essentially by forming the hydrogel in the presence of a plurality of liposomes such that the liposomes are dispersed throughout the bulk of the hydrogel, thereby lowering the friction coefficient of the resulting composition compared to the friction coefficient of the neat hydrogel (not having liposomes dispersed therein).
It should be noted that the capacity to lower the friction coefficient of any given hydrogel is based on the premise that the neat hydrogel is such that the notion of having a friction coefficient is relevant thereto, namely that the neat hydrogel is hard enough to allow its friction coefficient to be measured or assessed by conventional means.
According to some embodiments of the present invention, this method is applied to hydrogels or composite materials containing a hydrogel, which are characterized by a shear storage modulus (G′) of at least 1000 Pa.
In some embodiments, the method of incorporating liposomes in a hydrogel may be effected such that the tensile strength of the resulting composition is augmented thereby rendering the composition useful in applications in which the neat hydrogel was not.
Since a hydrogel can be characterized by its degree of crosslinking, which also correlated to its tensile strength and its ability to disperses and stabilize liposomes, the method of lowering the friction coefficient of a hydrogel is effected, according to some embodiments of the invention presented herein, for hydrogels which are characterized by having a molar percentage of the crosslinking agent that ranges from 0.00001% to 50% per hydrogel-forming agent total molar content. In some embodiments, the range of molar percentage of the crosslinking agent ranges from 0.01% to 25%, from 0.2% to 25%, from 1% to 20% or from 1% to 15%, as defined herein.
As demonstrated in the Examples section below, the ability to lower the friction coefficient of a hydrogel depends to some extent on the size of the liposomes dispersed therein. According to some embodiments of the present invention, the method is effected by forming the hydrogel in the presence of liposomes having an average diameter of at least 50 nm, at least 60 nm, at least 70 nm, at least 80 nm, at least 90 nm, at least 100 nm, at least 200 nm or at least 500 nm in diameter and larger, as defined herein.
As also demonstrated in the Examples section below, the ability to lower the friction coefficient of a hydrogel depends to some extent on the amount of liposomes dispersed therein.
According to embodiments of the present invention, the method is effected by forming the hydrogel in the presence of liposomes such that the final concentration of liposomes dispersed in the hydrogel is at least 1 mM, at least 2 mM, at least 4 mM, at least 6 mM, at least 10 mM, at least 12 mM, at least 16 mM, at least 20 mM, at least 24 mM, at least 30 mM, at least 35 mM, at least 40 mM, at least 60 mM, at least 100 mM, or at least 200 mM, as defined herein.
The method presented herein can be applied in cases where lowering the friction coefficient of a hydrogel, or a composite material containing a hydrogel, can benefit also from utilizing the capacity of liposomes to encapsulate and/or incorporation in their bilayer additional active agents, as this term is defined and exemplified hereinabove.
According to some embodiments of the present invention, applying the method for lowering the friction coefficient of a hydrogel or a composite material containing a hydrogel, namely incorporating liposomes in a hydrogel, may reduce the friction coefficient of the neat hydrogel by a factor of at least 2, a factor of at least 3, a factor of at least 5, a factor of at least 6, a factor of at least 7, a factor of at least 8, a factor of at least 9, a factor of at least 10, a factor of at least 12, a factor of at least 14, a factor of at least 16, a factor of at least 18, a factor of at least 20, a factor of at least 25, a factor of at least 30, a factor of at least 35, a factor of at least 40, a factor of at least 50 or by a factor of at least 60 or more.
It is noted herein that any type and/or size of the liposomes, their concentration in the hydrogel-forming composition, the chemical composition of the liposomes, the chemical composition of the hydrogel and the degree of crosslinking of the hydrogel, are according to any one of the embodiments described herein, in any combination.
Process of Manufacturing:
The process for manufacturing the hydrogel/liposomes compositions presented herein, or the process by which the method of lowering the friction coefficient of a hydrogel, is based on first manufacturing the liposomes according to the requirements and conditions discussed hereinabove (lipid composition, type and size, inclusion of polymers, inclusion of additional active agents etc.), and subsequently forming the hydrogel in the presence of these liposomes under the conditions discussed hereinabove (liposome concentration, degree of crosslinking, inclusion of fibrous materials and scaffold elements etc.).
According to an aspect of some embodiment of the present invention, there is provided a process for preparing the hydrogel/liposomes composition presented herein, which is carried out by:
Making or otherwise providing a plurality of liposomes as an aqueous suspension; and mixing the suspension with hydrogel-forming agent and a crosslinking agent, thereby obtaining the composition. The process may further makes use of an initiator, or a radical initiator agent, which is typically added to the liposome suspension. The process may further makes use of a catalyst which is typically added to the polymerization mixture.
Once all the ingredients are mixed together into a homogeneous mixture under conditions that maintain the integrity of the liposomes and all other components, the polymerization and the formation of the hydrogel is allowed to go to completion (cure), and the resulting composition can be molded, cut, processed and shaped into any desired shape.
Alternatively, the mixture of the pre-polymerized composition can be poured, cast, sprayed, coat or otherwise applied on or in a preformed substrate, and allowed to cure in situ.
Gelatin Methacrylate Hydrogels Encapsulating Liposomes:
The following is a representative embodiment of some embodiments of the present invention in which a pre-formed polymer is rendered crosslinkable by converting at least some of the units (monomers) therein into crosslinkable monomers having crosslinkable functional groups as described hereinabove.
While the representative embodiment is using gelatin as an exemplary pre-formed polymer, it is to be understood that other pre-formed polymers are also encompassed by embodiments of the present invention, and include, without limitation, polycaprolactone, peptides, polysiloxanes, hyaluronic acid, polysaccharides, chitosan, cellulose, alginate, polyglycols and any copolymer and mixes thereof.
According to an aspect of some embodiments of the present invention, there is provided a composition which includes a gelatin methacrylate-based hydrogel or a composite material containing a gelatin methacrylate-based hydrogel, and a plurality of liposomes dispersed throughout the bulk of the gelatin methacrylate-based hydrogel.
According to some embodiments, the gelatin methacrylate-based hydrogel of the composition or composite is characterized by a degree of methacrylation (DM) of amino groups in the gelatin, which is converted to gelatin methacrylate, which can be correlated to the “degree of crosslinking” as discussed hereinabove. A degree of methacrylation is typically assessed by percent of gelatin amino functional groups that underwent methacrylation out of the total number of the amino groups that can undergo methacrylation. As methacrylation correlated to the degree of crosslinking in the hydrogel, the higher the DM level, the more crosslinking is expected to occur in the hydrogel during curing. According to some of any of the embodiments of the present invention, the degree of methacrylation in the gelatin methacrylate-based hydrogels ranges from 10 percents to 90 percents and all the possible subranges as well as individual numerical values within that range. According to some embodiments, the degree of methacrylation is 5% or higher, 10% or higher, 20% or higher, 30% or higher, 40% or higher, 50% or higher, 60% or higher, 70% or higher, 80% or 90% or higher. According to some embodiments, the DM is about 75%.
The correlation between the “degree of methacrylation” to the “molar percent of a crosslinking agent to hydrogel-forming agent” can be calculated based on the number of lysine and hydroxylysine residues found in gelatin; these residues provide the amino functional groups in gelatin that undergo methacrylation. Since gelatin is known to contain 35 lysine and hydroxylisyne residues per 1000 residues (equivalent to 0.35 mmol amino groups per one gram of gelatin, or 0.35 M), it can be said that 3.5% of the monomers of gelatin can potentially undergo methacrylation. If 75% of these available amino groups undergo methacrylation, and every two methacrylic moieties form one crosslinking bond, the molar percent of a crosslinking agent to hydrogel-forming agent in the case of gelatin methacrylate-based hydrogels is about 3.5%*0.75/2=1.3%. At a DM of 50%, the molar percent of crosslinking is about 0.9%, and for a DM of 90% the crosslinking rate is about 1.6%.
According to some embodiments of the present invention, the degree of crosslinking of the liposome-containing degree of gelatin methacrylate-based hydrogels is about 0.2 molar percent or higher, about 0.3 molar percent or higher, about 0.5 molar percent or higher, about 0.7 molar percent or higher, about 0.9 molar percent or higher or about 1 molar percent or higher, based on the calculation presented hereinabove.
According to an aspect of some embodiments of the present invention, there is provided a method of lowering a friction coefficient of a gelatin methacrylate-based hydrogel or of a composite material containing a gelatin methacrylate-based hydrogel, the method being effected by forming the hydrogel in the presence of a plurality of liposomes.
According to some embodiments of any embodiment of the present invention, forming the gelatin methacrylate-based hydrogel encapsulating liposomes, as described herein, is such that the liposomes are dispersed throughout the bulk of the gelatin methacrylate-based hydrogel.
According to some embodiments, the composition or composite based on gelatin methacrylate-based hydrogel encapsulating liposomes, as described herein, is further characterized by a shear storage modulus (G′) of at least 1000 Pa, at least 1500 Pa, 2000 Pa, 2500 Pa, 3000 Pa or at least 4000 Pa.
According to some embodiments, the composition based on gelatin methacrylate-based hydrogel encapsulating liposomes, as described herein, is further characterized by an average diameter of the liposomes is larger than 60 nm, 70 nm, 80 nm, 90 nm, 100 nm, 150 nm or larger than 200 nm.
According to some embodiments, the concentration of liposomes in the gelatin methacrylate-based hydrogel ranges from 1 mM to 500 mM, or alternatively, the concentration of liposomes in the gelatin methacrylate-based hydrogel is higher than 4 mM, 8 mM, 12 mM, 16 mM, 20 mM, 30 mM, 50 mM, 100 mM, 150 mM, 200 mM, 250 mM, 300 mM, 40 mM or higher than 500 mM or higher.
According to some embodiments, the liposomes incorporated into the gelatin methacrylate-based hydrogel are being selected from the group consisting of SUV, LUV or MLV liposomes.
According to some embodiments, the liposomes incorporated into the gelatin methacrylate-based hydrogel include phosphatidylcholines such as DLPC, DMPC, DPPC, HSPC and/or DSPC.
According to some embodiments, the liposomes incorporated into the gelatin methacrylate-based hydrogel further include cholesterol at a concentration, in terms of molar percent relative to the total lipid composition of the liposome, that ranges from 1% to 50%, or from 1% to 40%, or from 1% to 10% and all the possible subranges as well as individual numerical values within that range, or 50% or lower.
According to some embodiments, the liposomes incorporated into the gelatin methacrylate-based hydrogel further include an additional agent selected from the group consisting of a polymer, cholesterol, liposome-stabilizing agent, a labeling agent, a bioactive agent and a therapeutically active agent, as these are defined herein in any one of the respective embodiments thereof.
According to some embodiments, the liposomes incorporated into the gelatin methacrylate-based hydrogel are prepared in the presence of a polymer, a liposome-stabilizing polymer, cholesterol and/or a liposome-stabilizing agent. According to some embodiments, the liposome-stabilizing agent is a polymer. According to some embodiments, the polymer can be poly(2-hydroxyethyl methacrylate) (pHEMA), alginate and hyaluronic acid (HA). In some embodiments, the concentration of the polymer in the liposome preparation solution ranges from 0.1 mg polymer per 1 ml of liposome suspension solution to 5 mg/ml and all the possible subranges as well as individual numerical values within that range.
According to some embodiments, the composite material containing a gelatin methacrylate-based hydrogel includes a material selected from the group consisting of a woven mesh of fibers, non-woven fibers, a plurality of rods and a net.
Applications:
As discussed hereinabove, the hydrogel/liposomes compositions presented herein can be used to make any type of article-of-manufacturing to be used in various applications. Such article-of-manufacturing can be a part of an implantable medical device or a drug-delivery system, and can take the form of any semi-solid or solid body, a disc, a fiber, a fabric, a tube, a film, a rod, a ring, a tubular mesh and any combination thereof.
The hydrogel/liposome compositions and composites, according to some of any of the embodiments of the present invention, can be used for the coating of a variety of substrates. An exemplary field of interest is the coating of medical articles for use in or on a bodily site, particularly catheters, guide wires or parts of such articles. As a coating material, the hydrogel/liposomes compositions can coat a part of an article-of-manufacturing or a device. Hence, the compositions presented herein may be used to completely or partially coat an implantable medical device, a drug-delivery system, any solid body, a disc, a fiber, a fabric, a tube, a film, a rod, a ring and/or a tubular mesh.
The capacity to maintain the mechanical properties, including shape and friction coefficient after a dehydration-rehydration cycle, renders the hydrogel/liposomes compositions presented herein particularly useful for manufacturing and/or coating parts and devices that are stored dry and used when the composition is fully hydrated.
Since hydrogels can be made from biocompatible materials and have many mechanical and chemical properties that mimic biological tissues, the compositions presented herein may be used to support and/or replace failing or degraded tissue in a living organism. For example, the composition may be used to manufacture parts of a joint-replacement implantable device, and replace cartilage that failed or degraded.
For another example, the composition presented herein can be used to coat the inner and outer surface of a tube a catheter, an orthodontic device or a stent, or in general used as a coating for low friction structural scaffolds which are used externally or internally (implantable), thereby allowing the practitioner to more freely manipulate the structural scaffoldon the path to and/or in the target organ or bodily site, and manipulate structural scaffold elements that are passed through a tube more effectively, as the friction coefficient of the inner and outer surfaces of the tube and/or the structural scaffold element are significantly reduced.
Other than providing a beneficial reduction in the friction coefficient, the incorporation of additional active agents in the hydrogel/liposomes composition, either as part of the liposomes or as part of the hydrogel, can assist beneficial processes and prevent undesired consequences while using the devices or articles-of-manufacturing which are based or using the composition. For example, if tissue regeneration and proliferation agents are added to the composition used in a joint-replacement device, the composition will serve a cartilage-mimicking substance while allowing the growth of host-cells in and around the composition. Alternatively, the additional agent(s) can prevent the formation of a biofilm or plaque on the surface of an implantable device coated by the compositions presented herein. Coating a catheter device or an implantable device with the composition presented herein which includes an antimicrobial agent will prevent an accidental infection that may be carried in by insertion of the device.
A Method of Treatment:
As discussed hereinabove, the hydrogel/liposomes compositions presented herein can be used in medical application to replace degraded tissue such as cartilage. Hence, according to an aspect of some embodiments of the present invention, there is provided a method of treating a living organism suffering from a medical condition associated with loss of or damaged cartilage, which is effected by replacing at least a portion of the damaged or missing cartilage with the hydrogel/liposomes composition presented herein.
It is noted herein that for any particular application and method of treatment, a specific combination of parameters will give an optimal composition. For example, in order to replace damaged cartilage, the composition should be characterized by suitable mechanical properties, particularly tensile strength and long-term durability, while exhibiting and maintaining (under load, temperature and duration) friction coefficient which resembles that of cartilage, and further contain additional active agents that will prevent undesired consequences, such as inflammation and infection, and promote beneficial processes such as self-tissue regeneration.
In the context of drug delivery, the compositions, composites and articles, according to some embodiments of the present invention, can be used to deliver and release a variety of bioactive and therapeutic agents which are useful in the treatment of a variety of medical conditions, including, without limitation, inflammation, infection, tumor suppression, bone tissue formation, tissue proliferation, metabolite and endocrine regulation, pain relief, and the likes.
It is expected that during the life of a patent maturing from this application many relevant hydrogels exhibiting a low friction coefficient will be developed and the scope of the term hydrogels exhibiting a low friction coefficient is intended to include all such new technologies a priori.
As used herein the term “about” refers to ±10%.
The terms “comprises”, “comprising”, “includes”, “including”, “having” and their conjugates mean “including but not limited to”.
The term “consisting of” means “including and limited to”.
The term “consisting essentially of” means that the composition, method or structure may include additional ingredients, steps and/or parts, but only if the additional ingredients, steps and/or parts do not materially alter the basic and novel characteristics of the claimed composition, method or structure.
As used herein, the singular form “a”, “an” and “the” include plural references unless the context clearly dictates otherwise. For example, the term “a compound” or “at least one compound” may include a plurality of compounds, including mixtures thereof.
Throughout this application, various embodiments of this invention may be presented in a range format. It should be understood that the description in range format is merely for convenience and brevity and should not be construed as an inflexible limitation on the scope of the invention. Accordingly, the description of a range should be considered to have specifically disclosed all the possible subranges as well as individual numerical values within that range. For example, description of a range such as from 1 to 6 should be considered to have specifically disclosed subranges such as from 1 to 3, from 1 to 4, from 1 to 5, from 2 to 4, from 2 to 6, from 3 to 6 etc., as well as individual numbers within that range, for example, 1, 2, 3, 4, 5, and 6. This applies regardless of the breadth of the range.
Whenever a numerical range is indicated herein, it is meant to include any cited numeral (fractional or integral) within the indicated range. The phrases “ranging/ranges between” a first indicate number and a second indicate number and “ranging/ranges from” a first indicate number “to” a second indicate number are used herein interchangeably and are meant to include the first and second indicated numbers and all the fractional and integral numerals therebetween.
As used herein the term “method” refers to manners, means, techniques and procedures for accomplishing a given task including, but not limited to, those manners, means, techniques and procedures either known to, or readily developed from known manners, means, techniques and procedures by practitioners of the chemical, pharmacological, biological, biochemical and medical arts.
As used herein, the term “treating” includes abrogating, substantially inhibiting, slowing or reversing the progression of a condition, substantially ameliorating clinical or aesthetical symptoms of a condition or substantially preventing the appearance of clinical or aesthetical symptoms of a condition.
It is appreciated that certain features of the invention, which are, for clarity, described in the context of separate embodiments, may also be provided in combination in a single embodiment. Conversely, various features of the invention, which are, for brevity, described in the context of a single embodiment, may also be provided separately or in any suitable subcombination or as suitable in any other described embodiment of the invention. Certain features described in the context of various embodiments are not to be considered essential features of those embodiments, unless the embodiment is inoperative without those elements.
Various embodiments and aspects of the present invention as delineated hereinabove and as claimed in the claims section below find experimental support in the following examples.
Reference is now made to the following examples, which together with the above descriptions illustrate some embodiments of the invention in a non limiting fashion.
Materials:
Water used in the experiments was purified using a Barnsted NanoPure systems to 18.2 MΩ cm resistance with total organic content levels of less than about 1 ppb.
All phosphatidylcholines lipids (PCs) were purchased from Lipoid, GmbH, and are listed in Table 1.
TABLE 1
Phase transition
temperature
Acronym
Full chemical name
MW
(Tm), ° C.
DLPC
1,2-dilauroyl-sn-glycero-3-
622
−1
phosphocholine
DMPC
1,2-dimyristoyl-sn-glycero-3-
677.9
23.2
phosphocholine
DPPC
1,2-dipalmitoyl-sn-glycero-3-
734.1
41.4
phosphocholine
HSPC
hydrogenated soybean
762.1
52.5
phosphocholine
DSPC
1,2-distearoyl-sn-glycero-3-
790.1
55
phosphocholine
2-hydroxyethylmethacrylate (2-hydroxyethyl 2-methylprop-2-enoate, also referred to herein as hydroxyethylmethacrylate or HEMA); ethylene glycol dimethacrylate , also referred to herein as 1,2-ethanediol dimethacrylate, ethylene dimethacrylate, ethane-1,2-diyl bis(2-methylacrylate) or EGDMA); ammonium persulfate (APS); N,N,N′,N′-tetramethylethylenediamine (TMEDA); and poly(ethylene glycol)n dimethacrylate, also referred to herein as poly(ethylene glycol) dimethacrylate, poly-EGDMA (9EGDMA is an exemplary crosslinking agent having an average molecular weight value of 550, which is equivalent to 9 repeating units of the monomer EGDMA, or poly(ethylene glycol)9 dimethacrylate); were purchased from Sigma-Aldrich and used as received.
Liposomes Preparation:
Multilamellar vesicles (MLV) composed of pure phosphatidylcholines, such as DLPC, DMPC, DPPC, HSPC and/or DSPC, were prepared by hydrating the lipids in pure water at a temperature of at least 5° C. above the lipid Tm. In order to dissolve HSPC and/or DSPC, 10% by volume of ethanol, heated to at least 5° C. above the Tm of the lipid, was added to the mixture before adding water.
In order to obtain unilamellar liposomes (SUV of less than 100 nm in diameter), MLVs were downsized by stepwise extrusion through polycarbonate membranes starting with a 400 nm and ending with 50 nm pore size membrane, using a Lipex 100 mL extruder system (Northern Lipids, Vancouver, Canada), heated to at least 5° C. above the lipid Tm.
SUV liposomes radii were measured using a Dynamic Light Scattering and showed a clear peak at 30±10 nm for all liposomes types immediately after their preparation. However, as discussed below, these small liposomes were not stable in term of their size, which grew over time, therefore the liposomes that were effectively used in the preparation of the low-friction hydrogels, according to embodiments of the present invention, exhibited a minimal average size of more than 80 nm in diameter.
Briefly, a Viscotek 802 (DLS) spectrophotometer was used in order to measure the liposomes radii in solution. Samples were diluted ten-fold and were measured about 12 times in the intensity distribution working mode. DLPC, DMPC and DPPC SUV liposomes showed a clear peak of radius of 30±10 nm when measured immediately after the liposome preparation. The radius tended to increase with time to about 60±10 nm. It has been noted that over time, an additional population of liposomes exhibiting much higher radius size, may appear in the measured samples. SUV HSPC liposomes measured immediately after their preparation showed higher radius values of about 40±10 nm. The SUV HSPC radius also increased with time.
Without being bound by any particular theory, it is noted that the trend of increasing SUV liposome radii over time is a consequence of preparing liposomes that lack stabilizing agents such as introducing PEG groups. Introducing PEGs cause steric repulsions and prevent liposomes from aggregating, without which, the radii values tend to grow with time together with appearance of another population having a higher radius, which did not exist immediately after the liposome preparation. This observation emphasizes the difficulties in working with small liposomes of less than 80 nm in diameter in aqueous solutions.
Hydrogel Preparation:
Neat hydrogels containing 1% crosslinking agent were prepared as follows: a hydrogel-forming monomer HEMA (3.2 grams), a crosslinking agent EGDMA (52.5 μL, 1% percent of the HEMA monomer's molar content), and an aqueous solution of the radical initiator agent APS (2 ml, 53 mM) were stirred vigorously for 30 minutes until fully mixed. Thereafter 50 μL of the catalyst TMEDA was added dropwise to the mixture, and the mixture was stirred for 20 seconds and poured into a 6 cm diameter Petri dish. The resulting hydrogels, having a thickness of about 1.8 mm, were allowed to crosslink (cure) over 4-5 hours, followed by rinsing in distilled water for 3 days to remove any unreacted materials while allowing full hydration of the hydrogel.
The crosslinked, hydrated and washed hydrogel samples were cut into about 1.8 mm thick discs having a diameter of about 5 mm (for the top piece) or 20 mm (for the bottom piece) for tribological tests and other characterization methods.
Preparations of neat hydrogels containing 1% 9EGDMA were prepared by replacing the EGDMA with the equivalent molar percentage of 9EGDMA.
Typical characteristics of the resulting exemplary hydrogels are a Young modulus that ranges from 0.65 MPa to 2 MPa; and a water content of 45%±5% by weight.
Hydrogels containing Liposomes:
Hydrogels incorporating liposomes therein were prepared similarly, while replacing the APS aqueous solution with a liposome suspension having the same APS content. The MLV liposomes' stock was prepared by adding 2 ml of the liposomes suspension at a concentration of 45 mM to an aqueous solution of the radical initiator agent. SUV liposomes suspension was prepared similarly at a concentration of 30 mM. It is noted herein that liposome suspensions can be prepared and maintained with other aqueous solutions at various concentrations, and added to the hydrogel-preparation mixture.
Table 2 below presents some exemplary compositions based on liposome-loaded hydrogels according to embodiments of the present invention, wherein the percent amount are given as weight percent with respect to the total weight of the composition, and the liposome concentration is denoted by the liposome concentration in the 2 ml suspension containing APS, which was used to prepare the hydrogel as presented hereinabove.
According to the exemplary hydrogel/liposome compositions demonstrated herein, the concentration of liposome in the original solution is diluted by 60% due to the addition of hydrogel-forming monomers. Therefore, in the case of the larger liposomes (MLV), their concentration in the hydrogel/liposome composition was about 18 mM (40% of the original 45 mM), while in the case of the smaller liposomes (SUV), their concentration in the final composition was about 12 mM (40% of 30 mM).
TABLE 2
Sample acronym
HEMA
HEMA
HEMA
HEMA
9EGDMA
HEMA
HEMA
EGDMA
EGDMA
9EGDMA
SUV
EGDMA 1%
EGDMA 2%
Component
Neat
Neat
Neat
DMPC
MLV HSPC
MLV HSPC
Monomer
HEMA
HEMA
HEMA
HEMA
HEMA
HEMA
Crosslinking agent
EGDMA
EGDMA
9EGDMA
9EGDMA
EGDMA
EGDMA
1%
2%
4%
4%
1%
2%
Radical initiator
APS
APS
APS
APS
APS
APS
agent
0.42%
0.42%
0.42%
0.42%
0.42%
0.42%
Catalyst
TMEDA
TMEDA
TMEDA
TMEDA
TMEDA
TMEDA
0.79%
0.79%
0.79%
0.79%
0.79%
0.79%
Liposomes
—
—
—
6.6 mM
10 mM
10 mM
Cryo-SEM Freeze Fracture Imaging:
Fresh hydrogel disc sample were flash-frozen (cryofixation), then fractured while maintained the sample at cryogenic (liquid nitrogen) temperature. Ice was removed by sublimation when formed on the cold fractured surface by increasing the temperature to about −100° C. for several minutes.
As can be seen in
As can be seen in
The SUV DMPC liposomes used to obtain the samples presented in
Young's Modulus Measurements:
a) Tensile Strength Measurements
Mechanical modulus measurements were performed using a Universal Testing Machine (UTM, Instron Corporation, Canton, Mass.). Cylindrical samples having dimensions of 6 mm diameter and 3 mm thickness were compressed between two flat plates to study their stress—strain relationships. Three different hydrogel samples were measured for each modulus determination.
As can be seen in
b) Compression Measurements Using a Rheometer
Compression measurements were performed using HAAKE Mars III Rheometer (Thermo Scientific). Cylindrical hydrogel samples having dimensions of 10 mm radius and 3.5±0.5 mm thickness were compressed by using a cone-and a plate configuration. Measurements were performed at 25° C. at velocity of 0.005 mm/sec.
Table 3 summarized the Young's modulus for exemplary hydrogels at compressions region of 0-10% and 0-20%.
TABLE 3
Sample name
Strain region
Young's Modulus
HEMA EGMA 0.1%
0-20%
0.29
Mpa
neat
HEMA EGMA 0.1% +
0-20%
0.2
Mpa
MLV HSPC
HEMA EGMA 0.5%
0-20%
0.47
Mpa
neat
HEMA EGMA 0.5% +
0-20%
0.33
Mpa
MLV HSPC
HEMA EGMA 1%
0-20%
0.74
Mpa
neat
HEMA EGMA 1% +
0-20%
0.65
Mpa
MLV HSPC
HEMA 9EGMA 4%
0-10%
1.9
Mpa
neat
HEMA 9EGMA 4% +
0-10%
1.9
Mpa
SUV DMPC
Dynamic Mechanical Characterization of Hydrogels:
Stemming from the dynamic mechanical tests, the storage modulus G′ and the loss modulus of the following HEMA hydrogels shown in
TABLE 4A
Sample name
G′ (Pa)
G″ (Pa)
HEMA EGMA 0.1%
3 × 104
5.4 × 103
neat
HEMA EGMA 0.1% +
4.6 × 104
5.8 × 103
MLV HSPC
HEMA EGMA 0.5%
3 × 104
5.3 × 103
neat
HEMA EGMA 0.5% +
6.7 × 104
8.8 × 103
MLV HSPC
TABLE 4B
Sample name
G′ (Pa)
G″ (Pa)
HEMA EGMA 1%
4 × 104
4.4 × 103
neat
HEMA EGMA 1% +
2.4 × 104
3.5 × 103
MLV HSPC
HEMA 9EGMA 4%
8.7 × 104
6.5 × 103
neat
HEMA 9EGMA 4% +
2.7 × 104
2.8 × 103
SUV DMPC
HEMA EGMA 2%
1.6 × 105
3.8 × 103
neat
HEMA EGMA 2% +
6.2 × 104
1.5 × 103
MLV DMPC
As can be seen in
Typical hydrogels used, for example, to dispense liposomes for drug delivery or hydrogels used as lubricants in aqueous conditions, typically exhibit a Young's moduli lower than 1000 Pa. These values indicate that these hydrogels are drastically distinct from the hydrogels used in embodiments of the present invention, since they are fragile, soft and “fluid like. Typically, soft hydrogels cannot be characterized using compression tests since these hydrogels shatter during the tests. Rheological tests, can be used to compare soft to hard hydrogels, based on their G′ and G” values.
Liposomal drug dispersed in hydrogels of carbopol 974, hydroxylethyl-cellulose (HEC) or a mixture of the two [Colloid and Surfaces B: Biointerfaces, 55, 2007, 212-221] typically exhibit G′ values in the range of 3-300 Pa, and G″ of 10-200 Pa. In temoporfin-loaded liposomal gels made from soybean lecithins for drug delivery onto topical and deeper skin layers [International Journal of Pharmaceutics, 373, 2009, 77-84], G′ values of 198.5-1046.7 Pa and G″ values range 192-330.7 Pa for the higher PC-content lipids. Another hydrogel system, prepared from egg phosphatidylcholine (EPC) liposomes in a poly(N-isopropylacrylamide) hydrogel showed values of G′ of about 750 Pa and G″ of 50-100 Pa for the hydrogel containing the EPC [Soft Matter, 8, 2012, 4517]. Hydrogel that composed of MLV's containing the ocular drug ofloxacin were examined [AAPS PharmSciTech, 10, 2009, 1336], and the rheological behavior of the hydrogel showed an elastic modulus G′ of 45 Pa. Formulation of vasoactive intestinal peptide (VIP) based on the incorporation of VIP-loaded rhodamine-conjugated liposomes within hyaluronic acid gel for the treatment of endotoxin-induced uveitis, showed values of G′=157-379 Pa and G″=127-236 Pa, at 1 Hz frequency [Journal of Controlled Release, 139, 2009, 22]. Other studies of hydrogel containing liposomes, such as the liposomal hydrogel based on Carbopol 940 [Romanian Biotechnological Letters, 16 (1), 2011, 47] and other liposomal gels for vaginal drug delivery, based on Carbopol 974P NF and Carbopol 980 NF [International Journal of Pharmaceutics, 219, 2001, 139], report only the flow properties of the gels indicating a fluid-like gel.
It is therefore noted herein that the hydrogels used in embodiments of the present invention exhibit G′ values which are much higher than the values exhibited by hydrogels reported in the literature.
Gel-to-gel friction tests were carried out using a CETR© tribometer, UMT model with a two sensors, one for loads in the range of 5-1000 g, and another one which enables application of high normal loads, in the range of 1-40 Kg. The set-up configuration was of a hydrogel on a hydrogel, in which both upper and lower samples are immersed in pure water. The pressure between the two samples was calculated according to the smaller surface, which was the upper hydrogel sample having a diameter of 5 mm. The hydrogel samples were subjected to relative sliding over a wide range of loads using two different sensors: sensor 1 applying loads of 10 to 500 grams and sensor 2 applying high loads of 1 to 4 Kg, whereas the high loads sensor simulated physiological joint pressures of 0.73±0.1 MPa to 8.75±1.25 MPa.
The testing parameters were as follows: Sliding velocity of 1 mm/sec, sliding amplitude of 1 mm and dwell time of 5 sec at each normal load before shearing commences. Experiments were conducted at room temperature (about 25±1° C.).
The static friction coefficient was obtained from the maximum value of the shear trace, and the kinetic friction coefficient was calculated as the average value at the sliding region, and the results were calculated as the mean of 2-3 independent experiments using 2-3 fresh pairs of hydrogel samples in each case, and 60 back-and-forth cycles per measurement.
The following figures show typical trace plots, obtained by a tribometer for symmetric (top and bottom) pure hydrogel samples. Different traces represent different load and pressures applied to the hydrogels. The trace plot marked by (a) in the following figures refers to a shear outline where sliding occurs. In such cases, the effective friction coefficient was calculated directly from the trace peak marked by “μ”. The peak “μ” is the dynamic friction, which is calculated as FL/FN, where FL is the lateral force, taken from the plateau region of the trace, and FN is the applied normal force. In cases where the static friction in the system is too high, sliding does not occur and the system is said to be in “rigid coupling”. In a rigid coupling scenario, the two surfaces move together and the trace plot exhibits a round sawtooth wave form. For example, in the examples presented herein, under relatively low pressures, such as 1-2 atmospheres, the system is in rigid coupling. The pressure in each load was calculated according to P=FN/A, where A is the contact area of the smaller (top) surfaces among the two opposing sample surfaces.
As can be seen in
As can be seen in
As can be seen in
As can be seen in
It is noted herein that exposing the exemplary HEMA EGDMA 1% hydrogel containing liposomes to relatively higher loads and/or an increased numbers of cycles may also lead to surface damage and rupture; however, the results presented herein demonstrate clearly the improved friction coefficient of the HEMA hydrogels upon introduction of liposomes therein.
Distribution of Liposomes in the Hydrogel:
In order to verify the shear reduction effect of adding liposomes to a hydrogel sample at various regions of the hydrogel, liposome suspensions were applied on top of the neat hydrogel sample surface, and the friction coefficient exhibited by such samples was compared to that obtained for a corresponding sample wherein the liposomes were incorporated into the bulk of the hydrogel prior and during the polymerization and crosslinking (gelation) process. In the measurements for hydrogel having liposomes on top of their surface, friction was measured between two HEMA EGDMA hydrogel samples while using the a corresponding liposome suspension of MLV HSPC as a medium between the samples, instead of using pure water, as used in the measurements of hydrogel samples having liposomes incorporated therein. Before measurements, the neat hydrogels were incubated with the liposome suspension to ensure the adsorption of the liposomes thereon. The comparative results are presented in
As can be seen in
It is noted herein that the friction coefficients measured after rinsing the neat hydrogels that adsorbed liposomes on their surface (rinsing was effected by immersing the samples in pure water overnight and applying direct flow of water thereon for several seconds) were raised to the values obtained for similar hydrogel samples measured in water without being in contact with liposomes (data not shown). These observations indicate that the incorporation of the liposomes into the hydrogel, rather than just being present on or between the hydrogel surfaces, plays an important role in the performance of the compositions according to embodiments of the present invention.
Sliding Velocity Tests:
As can be seen in
Table 5 presents the results of the gel-to-gel friction coefficient measurements for HEMA EGDMA 1% neat hydrogel sample pairs and HEMA EGDMA 1% hydrogel sample pair containing different types of MLV liposomes at a concentration of 45 mM: DMPC, DPPC, HSPC and DSPC. Data is based on two independent measurements for each pair of hydrogels. The left column represents the applied external load (in grams and the corresponding calculated pressure at the contact point under the given load. In this flat-to-flat system configuration, the pressure P was calculated by applying P=FN/A where A is the contact area of the smaller surface among the two discs, having a diameter of about 6 mm.
TABLE 5
Friction Coefficient
Hydrogel
HEMA
grams/
EGDMA
HEMA EGDMA
HEMA EGDMA
HEMA EGDMA
HEMA EGDMA
atmospheres
1% neat
1% MLV DMPC
1% MLV DPPC
1% MLV HSPC
1% MLV DSPC
10/0.034
0.55 ± 0.25
0.6 ± 0.18
0.31 ± 0.086
0.28 ± 0.06
0.28 ± 0.05
40/0.14
0.19 ± 0.05
0.25 ± 0.15
0.26 ± 0.067
0.093 ± 0.032
0.1 ± 0.025
200/0.7
—
0.28 ± 0.13
0.17 ± 0.043
0.078 ± 0.021
0.08 ± 0.016
400/1.4
—
—
0.12 ± 0.032
0.051 ± 0.014
0.06 ± 0.011
600/2.1
—
—
0.09 ± 0.027
0.039 ± 0.01
0.05 ± 0.013
1000/3.5
—
—
—
0.023 ± 0.005
0.024 ± 0.006
2000/7
—
—
—
0.013 ± 0.004
0.015 ± 0.003
3000/10.4
—
—
—
0.01 ± 0.002
0.01 ± 0.0022
As can be seen in Table 5, shear measurements showed a notable reduction of friction in the HEMA hydrogel samples when liposomes were incorporated therein. The dynamic friction coefficient was calculated from the shear traces as μ=FL/FN, where FN and FL are the measured normal and lateral forces in the system.
Hydrogel samples were measured using the tribometer in order to calculate the friction coefficient between the hydrogel sample and a metal head used in artificial hip ball-joint replacements.
In order to investigate the effect of adding liposomes to hydrogel on the hydrogel's friction coefficient, all hydrogel samples were measured using varying range of loads, corresponding to varying range of pressures. The different loads that were used were 40 grams, 150 grams, 500 grams, 1000 grams, and higher loads, wherein the highest load was limited by the breaking point of the hydrogel sample.
The pressure at each contact point was calculated according to the following method: when pressing the gel against the metal head formed an imprint on the hydrogel sample surface, typically in the high load tests, the radius r of the imprint was measured and the pressure was calculated as P=FN/πr2, where FN is the known applied normal load.
For the low load tests wherein no visible imprint was detected, geometrical calculations were applied to estimate the contact area as illustrated in
Typically, after shearing a hydrogel under high loads, an imprint appeared in the surface of the sample. Since the upper surface is a ball (and not a flat surface), the pressure at the contact point is not uniform, and has a certain distribution. Whenever an imprint has appeared, the size of the imprint was measured and used to calculate the pressure which formed that specific imprint. It is noted herein that when the pressure at the contact point has such a gradient, there may be a certain pressure value threshold that is required to form a visible depression in the hydrogel sample. However, the maximal pressure at the contact point is still higher, as the value from the imprint is still an average value.
Table 6 presents the pressure estimates for hydrogel samples for loads of 1 to 7 kg, comparing the estimates using the aforementioned A calculation to the estimates based on load imprint in the sample. The values in Table 6 are based on three different measurements from two different gels, having Young's moduli of 1.35±0.75 MPa.
TABLE 6
Calculated pressure (atmospheres)
Load (kg)
From Δ measurements
From imprint
1
5.6
5.64
2
7
11.3
3
9
16.9
4
11
22.6
5
12.8
28.2
6
15.4
34
7
18
40
The effective friction coefficient μ was measured by applying a certain normal load FN. The tribometer measurements afforded the lateral force FL from the sliding region in the trace. Dividing the lateral force by the normal force afforded the friction coefficient μ=FL/FN.
Sliding Velocity:
The following tables present the friction coefficient values measured between a hydrogel samples having a thickness of about 2 mm to a round metal head. The hydrogel composition is presented in the header row, while each column represents one hydrogel composition.
The testing parameters were as follows: sliding velocity of 1 mm/sec, sliding amplitude of 1.5 mm and dwell time of 5 seconds. Experiments were conducted at room temperature of 25±1° C., unless noted otherwise. The static friction coefficient was obtained from the maximum value of the shear trace (not shown), the kinetic friction coefficient was calculated as the average value at the sliding region, and the results were calculated as the mean of 1-3 independent experiments using a fresh hydrogel sample in each case, and 200 back-and-forth cycles per measurement. The “#” symbol represents measurements where the shear trace exhibited a sawtooth wave form, indicating rigid coupling between the two surfaces. In such cases the improvement in friction reduction due to the inclusion of liposomes in the hydrogel was greater than what is seen in the trace plots since the surfaces stick one to the other, and no sliding motion is present between the two surfaces. In other cases, due to the high loads the hydrogel broke down. Therefore, the “#” represents high friction either due to case of no sliding or/and mechanical failure of the hydrogel.
TABLE 7A
Load
EGDMA
EGDMA 0.1% +
EGDMA
EGDMA 0.5% +
(g)
0.1% Neat
MLV HSPC
0.5% Neat
MLV HSPC
40
0.63 ± 0.23
0.12 ± 0.027
0.64 ± 0.24
0.015 ± 0.006
150
0.4 ± 0.18
0.007 ± 0.02
0.44 ± 0.21
0.015 ± 0.007
500
#
0.004 ± 0.0164
#
0.015 ± 0.007
1000
0.039 ± 0.027
0.015 ± 0.008
2000
#
0.015 ± 0.008
TABLE 7B
Load g/
EGDMA
EGDMA 1% +
EGDMA 1% +
EGDMA 1% +
EGDMA 1% +
atmospheres
1% Neat
MLV HSPC
MLV DPPC
MLV DMPC
MLV DLPC
40/0.6
0.65 ± 0.15
0.04 ± 0.002
0.05 ± 0.002
0.04 ± 0.007
0.005 ± 0.008
150/1
0.55 ± 0.1
0.028 ± 0.0068
0.034 ± 0.008
0.03 ± 0.008
0.041 ± 0.008
500/2.5
0.55 ± 0.1
0.014 ± 0.0028
0.025 ± 0.0043
0.036 ± 0.005
0.005 ± 0.008
1000/5.7
0.55 ± 0.1#
0.011 ± 0.0048
0.026 ± 0.008
0.019 ± 0.008
0.045 ± 0.008
2000/11.3
0.011 ± 0.005
0.032 ± 0.009
0.04 ± 0.005
3000/16.9
0.011 ± 0.005
#
0.034 ± 0.01
#
As can be seen in Table 7B, the friction coefficient was reduced by a factor of about 50 under high pressures up to about 17 atmospheres.
TABLE 7C
Load
EGDMA
EGDMA 2% +
EGDMA 2% +
EGDMA 2% +
EGDMA 2% +
g/atm
2% Neat
MLV HSPC
MLV DPPC
MLV DMPC
MLV DLPC
40/0.6
1 ± 0.3
0.046 ± 0.015
0.09 ± 0.018
0.008 ± 0.0036
0.03 ± 0.01
150/1
0.66 ± 0.05
0.0245 ± 0.007
0.052 ± 0.012
0.006 ± 0.001
0.01 ± 0.002
500/2.5
0.66 ± 0.05
0.014 ± 0.004
0.037 ± 0.016
0.006 ± 0.001
0.01 ± 0.002
1000/5.7
0.66 ± 0.05#
0.01 ± 0.005
0.032 ± 0.013
0.006 ± 0.001
0.01 ± 0.002
2000/11.3
#
0.01 ± 0.005
0.029 ± 0.011
0.008 ± 0.001
0.01 ± 0.002
3000/16.9
#
0.011 ± 0.005
#
0.01 ± 0.0028
0.015 ± 0.002
4000/22.6
0.012 ± 0.0038
0.026 ± 0.01
5000/28.2
0.011 ± 0.0038
0.029 ± 0.01
6000/34
0.013 ± 0.0048
#
7000/39.5
0.012 ± 0.0047
TABLE 7D
Load
EGDMA
EGDMA 2% +
EGDMA 2% +
EGDMA 2% +
EGDMA 2% +
g/atm
2% Neat
SUV HSPC
SUV DPPC
SUV DMPC
SUV DLPC
40/0.6
1 ± 0.3
0.018 ± 0.005
0.043 ± 0.01
0.008 ± 0.003
0.058 ± 0.01
150/1
0.66 ± 0.05
0.0125 ± 0.0026
0.025 ± 0.013
0.008 ± 0.003
0.045 ± 0.01
500/2.5
0.66 ± 0.05
0.01 ± 0.0025
0.017 ± 0.006
0.01 ± 0.005
0.05 ± 0.01
1000/5.7
0.66 ± 0.05#
0.017 ± 0.008
0.017 ± 0.008
0.021 ± 0.006
0.045 ± 0.01
2000/11.3
#
0.01 ± 0.005
#
0.02 ± 0.0046
0.045 ± 0.01
3000/16.9
#
0.011 ± 0.005
0.018 ± 0.007
0.049 ± 0.01
4000/22.6
#
0.015 ± 0.0038
#
5000/28.2
0.0135 ± 0.0034
TABLE 8A
Load
9EGDMA
9EGDMA 4% +
9EGDMA 4% +
9EGDMA 4% +
9EGDMA 4% +
kg/atms
4% neat
MLV HSPC
MLV DPPC
MLV DMPC PC
MLV DLPC DM PC
1/5.7
0.3 ± 0.015
0.02 ± 0.008
0.03 ± 0.01
0.019 ± 0.009
0.019 ± 0.01
2/11.3
#
0.013 ± 0.0045
0.025 ± 0.01
0.015 ± 0.008
0.07 ± 0.02
3/16.9
0.012 ± 0.005
0.03 ± 0.01
0.03 ± 0.01
0.081 ± 0.03
4/22.6
0.011 ± 0.003
#
0.039 ± 0.01
#
TABLE 8B
Load
9EGDMA
9EGDMA 4% +
9EGDMA 4% +
9EGDMA 4% +
9EGDMA 4% +
kg/atms
4% neat
SUV HSPC
SUV DPPC
SUV DMPC PC
SUV DLPC DM PC
1/5.7
#
0.033 ± 0.01
0.02 ± 0.006
0.012 ± 0.003
#
2/11.3
0.026 ± 0.008
0.018 ± 0.01
0.018 ± 0.009
3/16.9
0.03 ± 0.01
0.04 ± 0.01
0.018 ± 0.008
4/22.6
#
#
0.014 ± 0.008
5/28.2
0.014 ± 0.006
As can be seen in
Liposomes in Hydrogel Versus Lipids in Hydrogel:
In order to demonstrate the effect of liposomes incorporation into hydrogels, according to embodiments of the present invention, compared to the effect of adding the lipids comprising these liposomes (i.e., not in liposome configuration) to a comparable hydrogel, friction measurements were conducted with hydrogels prepared with the corresponding lipids without attempting to form liposomes therewith.
HEMA EGDMA 1% hydrogels were prepared with HSPC lipids rather than HSPC liposomes. The HSPC lipid solution was prepared by dissolving 375 mg HSPC lipid in 10 ml of pure water (the same amount of lipids that was used to prepare MLV HSPC liposomes). Heating, sonication or vortex mixing were not applied.
When subjecting the samples described above to gel-to-metal friction coefficient measurements, the HEMA EGDMA 1% hydrogels prepared with HSPC lipids exhibited an increase of the friction coefficient by a factor of about 5 compared to the results obtained for the corresponding samples prepared with MLV HSPC liposomes (data not shown). For example, the friction coefficient exhibited by the lipid-containing hydrogels was 0.055-0.05, under loads of 1000-2000 grams respectively, compared with values of 0.011/0.011 which were measured for the equivalent HEMA EGDMA 1% containing MLV HSPC liposomes incorporated therein. Moreover, the HEMA EGDMA 1% hydrogel prepared with HSPC lipid suffered a mechanical failure (broke) under a load of 3000 grams after less than 60 seconds, while the equivalent hydrogel sample containing MLV HSPC liposomes sustained the same load for 300 seconds and was whole after the measurement.
Hydrogels were dried by heating to 60° C. in an oven for several days until hydrogels were completely dry, as determined by achieving a constant sample weight for several hours. Thereafter, the fully dehydrated hydrogel samples were rehydrated in pure water by immersion. After the hydrogel samples were fully swollen (hydrated), the samples were subjected to friction measurements in a tribometer, similar to the friction measurements presented hereinabove.
As can be seen in
As can be seen in
Duration of the Effect of Adding Liposomes to Hydrogels:
The hydrogel/liposomes compositions, according to embodiments of the present invention, were tested for their capability to effectively maintain their low friction coefficient over extended periods of time.
Exemplary hydrogel/liposomes compositions, presented in Table 9 below, were measured in the tribometer for time period exceeding 300 seconds to evaluate the capacity of the compositions to reduce friction for extended periods of time.
TABLE 9
Sample
Load
Result
Neat HEMA EGDMA 2%
3 kg
Mechanical failure after
hydrogel
5 minutes
Neat HEMA 9EGDMA 2%
3 kg
Mechanical failure after
hydrogel
45 minutes
HEMA EGDMA2% +
3 kg
Sample intact after 1 hour
MLV HSPC
μ = 0.015 ± 0.005
HEMA 9EGDMA 2% +
3 kg
Sample intact after 1 hour
MLV HSPC
μ = 0.015 ± 0.005
As can be seen in Table 9, the incorporation of liposomes into a hydrogel sample not only confers a notable reduction in their friction coefficient, but also confers a notable increase in the length of service (longevity) of the hydrogel, according to embodiments of the present invention.
Reduction of Friction at Human Body Temperature:
To verify that the hydrogel/liposomes compositions according to embodiments of the present invention are useful for biomedical applications, friction coefficients of samples of the exemplary HEMA EGDMA 1%+MLV HSPC hydrogels, were measured in a tribometer under loads ranging from 40 grams to 3 kg, while setting the tribometer thermostat to 37° C. in a gel-to-metal setting as described hereinabove (See, Table 10 below).
Table 10 presents the long-term friction measurements conducted at human body temperatures using the exemplary HEMA EGDMA 1%+MLV HSPC hydrogel samples.
TABLE 10
Sample
Load
Result
Neat HEMA EGDMA
2 kg
Mechanical failure after
1% hydrogel
2400 seconds
HEMA EGDMA 1% +
2 kg
Sample intact after 1 hour
MLV HSPC
μ = 0.009 ± 0.005
As can be seen in Table 10, until the hydrogel samples experienced mechanical failure due to the high pressure in the system, the friction coefficients exhibited by these hydrogels were similar to those measured for identical samples at 25° C.±1° C.
Preparation Method:
Neat hydrogels containing 4% crosslinking agent were prepared as follows: a hydrogel-forming monomer, Methacrylamide (2.1 grams), a crosslinking agent 9EGDMA (560 μL, 4% percent to the monomer molar content), and an aqueous solution of the radical initiator agent APS (24 mg, 10 ml) were stirred vigorously for 30 minutes until fully mixed. Thereafter, 50 μL of the catalyst TMEDA was added dropwise to the mixture and the mixture was stirred for 20 seconds and poured into a 6 cm diameter Petri dish. The rinsing procedure followed similar steps as described hereinabove.
The sample based on methacrylamide are referred to herein as MAAm 9EGDMA 4% neat and MAAm 9EGDMA 4%+liposomes, e.g., MAAm 9EGDMA 4%+SUV DMPC.
Friction Reduction Measurements:
The reduction in friction coefficient upon inclusion of SUV DMPC liposome solution within the hydrogel is shown in Table 11 below.
TABLE 11
MAAm
MAAm
Load
9EGMA 4%
9EGMA 4% +
[g]
neat
SUV DMPC
40
0.25 ± 0.1
0.0155 ± 0.005
150
0.077 ± 0.03
0.017 ± 0.005
300
0.075 ± 0.03
0.022 ± 0.005
500
0.085 ± 0.03
0.014 ± 0.0045
Rheological characteristic of a sample of MAAm 9EGDMA 4%+SUV DMPC hydrogel, namely storage and loss moduli, are shown in Table 12.
TABLE 12
Sample name
G′ (Pa)
G″ (Pa)
MAAm 9EGMA 4%
1.2 × 104
864
neat
MAAm 9EGMA 4% +
1.64 × 104
808
SUV DMPC
As can be reckoned from the results presented above, the concept of incorporating liposomes into hydrogels is valid for hydrogels of various types. In the case presented above, the MAAm-based hydrogels incorporating liposomes therein exhibited reduction in the friction coefficient of 3-6 fold, compared to the corresponding HEMA-based hydrogel.
Preparation Method:
HEMA monomer was mixed with polycaprolactone (PCL, Sigma, Mw=45,000), by heating to 60° C. while stirring until the mixture solution is clear. Thereafter, 9 ml of HEMA mixed with 27 mg of PCL gave a 3% HEMA/PCL mixture, which was diluted by adding more HEMA to achieve a 1% HEMA/PCL mixture.
After cooling the mixture to room temperature, 3 ml from the mixed HEMA/PCL solution was mixed with 24 mg APS, 50 μL EGDMA, 50 μL TMEDA and 2 ml of water or liposome suspension to afford HEMA/PCL hydrogel samples.
Friction Reduction Measurements:
These hydrogels were measured with the tribometer in the gel-to-metal configuration, and the friction reduction results are shown in Table 13.
TABLE 13
HEMA/
HEMA/
PCL 1%
HEMA/PCL 1%
PCL 3%
HEMA/PCL 3%
Load
EGDMA
EGDMA 1% +
EGDMA
EGDMA 1% +
[g]
1% neat
MLV HSPC
1% neat
MLV HSPC
1000
0.27
0.012 ± 0.005
0.26
0.009 ± 0.005
2000
#
0.01 ± 0.003
#
0.0108 ± 0.005
Table 14 summarizes rheometer measurements of the hydrogels describing the dynamic modulus properties.
TABLE 14
Sample name
G′ (Pa)
G″ (Pa)
HEMA/PCL 1% EGDMA
1.1 × 105
1.9 × 104
1% neat
HEMA/PCL 1% EGDMA
1.38 × 105
2.4 × 104
1% + MLV HSPC
HEMA/PCL 3% EGDMA
5 × 104
1 × 104
1% neat
HEMA/PCL 3% EGDMA
7 × 104
1.34 × 104
1% + MLV HSPC
As can be reckoned from the results presented above, the concept of incorporating liposomes into hydrogels is valid for hydrogels which include polymers which do not participate in the network but are rather entangled therein. In the case presented above, the incorporating liposomes in HEMA-based hydrogels, containing polycaprolactone which is entangled rather than chemically bound to the hydrogel' s network, reduced the friction coefficient by a factor of 20 and more.
The results presented below were obtained for HEMA EGDMA 2% hydrogels, which incorporate liposomes which were prepared in a solution of 0.1 mg/ml of hyaluronic acid (HA) (Sigma, Mw of 8,000-15,000 g/mol) rather than in pure water, as described hereinabove.
Table 15 presents the friction coefficient measured between exemplary hydrogel/liposome compositions to a metal head under different loads and pressures at 25° C.
TABLE 15
HEMA
HEMA
HEMA
EGDMA
EGDMA
Load
EGDMA 2%
2% + MLV
2% + MLV
g/atm
Neat
DMPC/HA
HSPC/HA
150/1
0.66 ± 0.05
0.048 ± 0.027
0.007 ± 0.002
500/2.5
0.66 ± 0.05
0.036 ± 0.02
0.006 ± 0.0025
1000/5.7
0.66 ± 0.05#
0.026 ± 0.013
0.0067 ± 0.003
3000/16.9
#
0.022 ± 0.01
0.0073 ± 0.003
5000/28.2
0.028 ± 0.012
7000/39.5
0.032 ± 0.013
Table 16 presents the friction coefficient measured between exemplary hydrogel/liposome compositions to a metal head under different loads and pressures at 37° C.
TABLE 16
Load
EGDMA 2%
EGDMA 2% + MLV
EGDMA 2% +
g/atm
Neat
DMPC/HA
MLV HSPC/HA
150/1
0.66 ± 0.05
0.026 ± 0.012
0.0076 ± 0.005
500/2.5
0.66 ± 0.05
0.036 ± 0.016
0.0076 ± 0.005
1000/5.7
0.66 ± 0.05#
0.03 ± 0.012
0.008 ± 0.004
3000/16.9
#
0.046 ± 0.018
0.01 ± 0.0046
As can be seen in Tables 15 and 16, liposomes prepared in the presence of a polymer, such as HA, were used successfully in reducing the friction coefficient of hydrogels.
The results presented below demonstrate the effect of liposome concentration of the capacity of the liposomes to reduce the friction coefficient of hydrogels, according to embodiments of the present invention. For this purpose, HEMA 9EGDMA 4% hydrogels were prepared as described hereinabove, using stock liposome solutions having various concentrations of SUV DMPC liposomes.
Table 17 presents the results of friction coefficients measurements obtained for hydrogel/liposome composition samples against a metal head under different loads and pressures at 25° C.
TABLE 17
HEMA
HEMA
HEMA
HEMA
HEMA
9EGDMA 4% +
9EGDMA 4% +
9EGDMA 4% +
9EGDMA 4% +
Load
9EGDMA 4%
SUV DMPC
SUV DMPC
SUV DMPC
SUV DMPC
Kg/atm
Neat
1.6 mM
4 mM
6 mM
12 mM
1/5.6
0.3 ± 0.05
0.04 ± 0.019
0.045 ± 0.017
0.03 ± 0.012
0.013 ± 0.005
3/16.9
0.125 ± 0.07
0.1 ± 0.07
0.039 ± 0.013
0.015 ± 0.003
5/28.2
0.045 ± 0.019
0.014 ± 0.008
As can be seen in Table 17, augmenting the concentration of liposomes in the hydrogel/liposomes compositions, according to embodiments of the present invention, had a notable impact on their capacity to reduce the friction coefficients of the tested compositions. In the low concentration range of 1.6 to 6 mM, a reduction in the friction coefficient by a factor ranging from 7.5 to 10, respectively, was observed. A far more notable reduction by a factor of 60 was observed for the sample prepared with 12 nM liposomes, indicating a non-linear and possibly cumulative effect of several combined factors which change along with the liposome concentration, such as the water inclusion/exclusion, density and the likes.
The experiment described below was designed to study the effect of the degree of crosslinking on the capacity of liposomes to reduce the friction coefficient of hydrogels. Thus, HEMA hydrogels having a 60:40 HEMA:water ratio were prepared with 0.2% EGDMA and SUV DMPC liposomes having an average diameter of 80±20 nm at a concentration of about 2 mM. An corresponding neat hydrogel was prepared as control, and the samples were subjected to shear measurements under loads of 500 grams to 1 Kg and higher.
The results showed that both neat and HEMA EGDMA0.2+SUV DMPC hydrogels were in rigid coupled over the entire range of loads, showing similar friction coefficients for both hydrogels. These results indicate that at such low degree of crosslinking and liposome size, no enhanced shear reduction of the hydrogel was obtained.
The exemplary neat HEMA EGDMA 2% and the exemplary corresponding hydrogel having DMPC MLV liposomes incorporated therein were subjected to long run friction measurements. The hydrogels were rubbed back and forth at amplitude of 1.5 mm against a metal head in a water bath at 25° C.
A capacitance probe was connected at all times during the shear measurements and monitored and recorded the height of the sample.
As can be seen in
The height of the exemplary sample of HEMA EGDMA 2% hydrogel having DMPC MLV liposomes incorporated therein decreased by only 14.5 microns at the end of the 60 minutes run.
Wear tests were performed under lower normal load of 1 kg which was applied on different hydrogel samples while shearing against a metal head in pure water at T=25° C. for 2 hours, and the results are presented in
The wear of the neat HEMA hydrogel sample was higher (57 microns; not shown) compared to the corresponding sample having HSPC MLV liposomes incorporated therein (12 microns; not shown) and the sample having DMPC MLV liposomes incorporated therein (no wear) hydrogels.
The rheological and tribological properties of HEMA hydrogels with MLV hydrogenated soy phosphatidylcholine (HSPC) and MLV DMPC liposomes, which were prepared in the presence of a polymer prior to the hydrogel-encapsulation step, were tested.
The exemplary polymers used in the preparation of the liposomed were poly(2-hydroxyethyl methacrylate) (pHEMA), alginate and hyaluronic acid.
Materials:
Water used was purified Barnsted NanoPure systems to 18.2 MΩ cm resistance with total organic content levels of less than about 1 ppb. All phosphatidylcholines lipids were purchased from lipoid, GmbH. 2-hydroxyethyl methacrylate (HEMA), ammonium persulfate (APS), N,N,N′,N′-tetramethylethylenediamine (TMEDA), ethylene glycol methacrylate (EGDMA) were purchased from Sigma-Aldrich and used as received. All polymers, poly(2-hydroxyethyl methacrylate) (pHEMA) of average Mw of 20,000 g/mol, hyaluronic acid sodium salt from rooster comb and alginic acid sodium salt from brown algae medium viscosity, were purchased from Sigma-Aldrich.
Liposomes Preparation:
Multilamellar vesicles (MLV) composed of 1,2-dimyristoyl-sn-glycero-3-phosphocholine (DMPC) and HSPC were prepared by hydrating the lipids in at least 5° C. above the lipid TM, followed by sonication. Where liposomes were prepared in the presence of a polymer, the polymer solution was prepared in advance at a polymer concentration of 1 mg/1 ml, and after full dissolution of the polymer, the polymer solution was heated at least 5° C. above the lipid TM and added to the lipids, followed by mixing.
Hydrogel Preparation:
Neat hydrogels containing 2% (molar percent with respect to the monomer) crosslinking agent were prepared as follows: HEMA (3.2 g), EGDMA (100 mg) and APS aqueous solution (2 ml, 53 mM) were vigorously stirred for 30 minutes until fully mixed. TMEDA (50 μl) was added to the mixture, stirred for 20 seconds and poured into a 6 cm diameter petri dish. The gels were allowed to crosslink over 4-5 hours, followed by rinsing in distilled water for 3 days to remove unreacted materials. The obtained gels, referred to as HEMA EGDMA 2%, were cut into pieces for tribological tests and other characterization methods. Liposome-loaded hydrogels were prepared similarly. The APS aqueous solution was replaced by a liposome suspension with the same APS content.
Liposome Size and Zeta Potential Measurements:
Size and zeta potential of the different liposomes in pure water and in different polymer solutions at concentration of 1 mg/ml were determined using the Malvern Zetasizer. Briefly, Zeta (ξ) potential is a measure of the surface electrical charge of particles, and is often being used to characterize colloids. Zeta (ξ) absolute value 5 mV or higher indicates on a charged surface of the colloid, which corresponds to stable colloidal dispersion as a result from repealing interactions between two colloids.
Table 18 presents Zeta potential measurements of the different polymer solutions in pure water and when mixed with DMPC and HSPC liposomes, as measured for neat HEMA EGDMA 2% hydrogel, HEMA EGDMA 2%+MLV HSPC 45 mM and HEMA EGDMA 2%+MLV DMPC 45 mM.
TABLE 18
Zeta potential values for the neat polymer
and the mixed polymer/liposome solutions
+MLV
polymer
Neat hydrogel
HSPC 45 mM
+MLV DMPC 45 mM
pHEMA
−20 ± 5 mV
zero
zero
Alginate
−50 ± 12 mV
−16 ± 7 mV
−19 ± 7 mV
HA
−30 ± 5 mV
zero
zero
As can be seen in Table 18, MLV's with pHEMA or HA polymer dispersions showed a zero value of ξ (meaning |ξ|<5 mV) as MLV's with alginate showed a negatively charged zeta (Table 1).
Size measurements of the samples indicates that the MLV DMPC liposomes in pure water have three populations of D1=35±5 nm, D2=122±14 nm and D3=570±79 nm. DLS data of the MLV HSPC liposomes showed D=550±100 nm.
Table 19 presents DLS measurements of the various MLV HSPC and MLV DMPC liposome suspensions in pure water and in different polymers.
TABLE 19
DLS
measuremen
MLV HSPC
MLV DMPC
pure water
540 ± 100 nm
35 ± 5 nm, 122 ± 14 nm, 570 ± 79 nm
pHEMA
474 ± 60 nm
—
Alginate
635 ± 135 nm
622 ± 250 nm
HA
580 ± 230 nm
180 ± 75 nm, 630 ± 190 nm
As can be seen in Table 19, mixing MLV DMPC with HA and alginate as polymers result in smaller particle size, as the population of size of 35±5 nm disappeared upon mixing. The difficulty in measuring the size of the pHEMA/MLV DMPC suspension indicates a plurality of size populations.
Cryo-SEM Freeze Fracture Imaging:
Fresh samples were flash frozen to afford cryofixation, and then fractured by breaking the solid sample while maintained at liquid nitrogen temperature. The cold fractured surface sometimes “etched” by increasing the temperature to about −100° C. for several minutes to let some ice sublime.
The neat HEMA EGDMA 2% sample, the HEMA EGDMA 2%+MLV DMPC/polymer sample and the HEMA EGDMA 2%+MLV HSPC/polymer sample were imaged. These freeze fracture images of the hydrogel with liposomes/polymer showed no significantly different from the freeze fracture images of the HEMA with liposomes prepared with no added polymer for each of the liposome type (images not shown).
Dynamic Mechanical Characterization of Hydrogels:
Samples were subjected to a strain sweep test in which they were deformed at different shear strains, and the moduli were recorded to define the linear viscoelastic zone in which the modulus G′ is independent of the applied strain. Each sample was then subjected to a frequency sweep test. A sinusoidal deformation of constant peak amplitude was applied over the range of frequencies from 0.05-100 Hz under a stress of 50 Pa at 25° C.
Table 20 presents the result of the frequency sweep test of a HEMA EGDMA 2% hydrogels.
TABLE 20
HEMA
Pure water
pHEMA
Alginate
HA
EGDMA 2%
+HSPC
+DMPC
+HSPC
+DMPC
+HSPC
+DMPC
+HSPC
+DMPC
G′ [Pa]
6.3 × 104
6.2 × 104
1.3 × 105
1.1 × 105
7.8 × 104
7.4 × 104
4.2 × 104
3.2 × 104
G″ [Pa]
1.3 × 104
1 × 104
2.7 × 104
8 × 103
2 × 104
1.2 × 104
6.5 × 103
5.2 × 103
As can be seen in Table 20, the storage shear modulus, G′ was higher than the loss shear modulus, over the entire frequency region indicating that the elastic response of the material is stronger than the viscous response, representative of a solid-like behavior. The storage modulus was fairly constant throughout the entire frequency range, although a slight increase is observed with increasing frequency.
Friction Measurements Gel vs. Metal Head:
Friction tests were carried out using a CETR© tribometer, UMT model with a high sensor which enables application of high normal loads. HEMA hydrogels were measured using the tribometer in order to calculate the friction coefficient between the hydrogel to a metal head used in artificial hip joint replacements.
In order to investigate the hydrogels' friction coefficient, all hydrogels were measured using varying range of loads, corresponding to varying range of pressures. The different loads that were used were: 40 g, 150 g, 500 g, 1000 g, and also higher loads—the highest load was limited by the breaking point of the hydrogel. The pressure at each contact point was calculated as described hereinabove. The effective friction coefficient μ was measured by applying a certain normal load FN and using the tribometer obtained directly the lateral force FL from the sliding region in the trace. Dividing the lateral force by the normal force affords the friction coefficient μ=FL/FN.
The testing parameters were as follows: sliding velocity of 1 mm/sec, sliding amplitudes of 1-1.5 mm and dwell time of 5 seconds. Experiments were conducted at temperature of 37±1° when samples were immersed in pure water. The kinetic friction coefficient was calculated as the average value at the sliding region, and the results were calculated as the mean of 2-5 independent experiments using a fresh hydrogel sample in each case, and 300 back-and-forth cycles per measurement.
Unless stated otherwise, the “#” symbol used in any of the figures presented in this document represents measurements where the shear trace exhibited a sawtooth wave form, indicating rigid coupling between the two surfaces. In such cases the improvement in friction reduction due to the inclusion of liposomes in the hydrogel was greater than what is seen in the trace plots since the surfaces stick one to the other, and no sliding motion is present between the two surfaces. In other cases, due to the high loads the hydrogel broke down. Therefore, the “#” represents high friction either due to case of no sliding or/and mechanical failure of the hydrogel.
As can be seen
Moreover, the addition of DMPC/polymer complexes to the HEMA hydrogels resulted in a tendency of the hydrogel to sustain much higher pressures in comparison to the hydrogels containing MLV DMPC liposomes (without a polymer). The HEMA hydrogels with MLV DMPC broke after increasing the pressure above 16.9 atm while the HEMA hydrogels with MLV DMPC with pHEMA/HA sustain much higher pressures up to 39.5/28.2 atm, respectively.
Table 21 and Table 22 summarize the results of the friction coefficient measurements described hereinabove for the DMPC MLV and the HSPC MLV liposomes respectively, comparing hydrogel containing the same while prepared with and without the presence of various polymers, according to some embodiments of the present invention.
TABLE 21
Load [Kg]/
+MLV DMPC/
+MLV DMPC/
+MLV DMPC/
P [atm]
neat
+MLV DMPC
pHEMA
HA
Alginate
0.15/1
0.6 ± 0.05
0.03 ± 0.01
0.017 ± 0.005
0.03 ± 0.005
0.008 ± 0.005
0.5/2.3
0.6 ± 0.05
0.033 ± 0.01
0.017 ± 0.005
0.022 ± 0.005
0.007 ± 0.005
1/5.6
0.035 ± 0.01
0.017 ± 0.005
0.027 ± 0.005
0.006 ± 0.005
3/16.9
0.035 ± 0.01
0.025 ± 0.005
0.022 ± 0.005
0.0074 ± 0.005
5/28.2
0.024 ± 0.005
0.02 ± 0.005
7/39.5
0.023 ± 0.005
TABLE 22
Load [Kg]/
+MLV HSPC/
+MLV HSPC/
+MLV HSPC/
P [atm]
neat
+MLV HSPC
pHEMA
HA
Alginate
0.15/1
0.6 ± 0.05
0.01 ± 0.005
0.06 ± 0.005
0.021 ± 0.005
0.027 ± 0.005
0.5/2.3
0.6 ± 0.05
0.0118 ± 0.005
0.039 ± 0.005
0.014 ± 0.005
0.02 ± 0.005
1/5.6
0.014 ± 0.005
0.022 ± 0.005
0.021 ± 0.005
0.05 ± 0.005
3/16.9
0.016 ± 0.005
0.024 ± 0.005
0.025 ± 0.005
0.044 ± 0.005
Wear Measurements:
Neat HEMA EGDMA 2%, HEMA EGDMA 2%+MLV DMPC and HEMA EGDMA 2% encapsulating MLV DMPC prepared in the presence of pHEMA (HEMA EGDMA 2%+MLV DMPC/pHEMA), according to some embodiments of the present invention, were subjected to long run friction measurements. The hydrogels were rubbed back and forth at amplitude of 1.5 mm against a metal head in a water bath at 37°. A capacitance probe was connected all time during the shear measurements and monitored and recorded the height of the sample. The neat hydrogel exhibited continues reduction in the height of the sample, and during 44 minutes of sliding, before the sample was crushed, a reduction of about 100 microns was recorded. The HEMA EGDMA 2%+MLV DMPC/pHEMA sample showed a remarkable resistance to wear as during the first 60 minutes of shearing the reduction of the height of the sample was of only about 3 microns. The friction coefficient of the HEMA EGDMA 2%+MLV DMPC/pHEMA sample during 2 hours of shearing was of 0.015±0.005, and the sample remained intact. The HEMA EGDMA 2%+MLV DMPC sample showed a reduction of about 100 microns in height of the sample after 1 hour of measurement. The friction coefficient during 1 hour of measurement was of 0.04±0.015, and after about 71 minutes the sample broke.
The effect of the level of crosslinking of hydrogels containing different concentrations of SUV or MLV liposomes, on the friction coefficient μ of the hydrogel/liposome composition was investigated at different temperatures T=25° C. and T=37° C.
Neat HEMA hydrogels containing 2%, 1%, 0.22% and 0.1% (molar percent with respect to the monomer) crosslinking agent were prepared as follows: HEMA (3.2 g), EGDMA (100 mg, 50 mg, 11 mg, and 5 mg) and APS aqueous solution (2 ml, 53 mM) were vigorously stirred for 30 minutes until fully mixed. TMEDA (50 μl) was added to the mixture, stirred for 20 seconds and poured into a 6 cm diameter petri dish. The gels were allowed to cure over 4 hours, followed by rinsing in distilled water for 3 days to remove unreacted materials.
The obtained gels were cut into pieces for tribological tests and other characterization methods. Liposome-loaded hydrogels were prepared similarly. The APS aqueous solution was replaced by a liposome suspension with the same APS content.
Varying Concentration of Small Unilammelar Vesicles (SUVs):
HEMA hydrogels containing different concentrations of SUV DMPC and SUV HSPC (diameter range from 56-70 nm for the SUV DMPC, and 76-116 nm for the SUV HSPC liposomes) liposomal hydrogels ranging from zero (neat hydrogel) to 12 mM were prepared as described hereinabove. Due to differences in the molecular weights of the DMPC and the HSPC lipids, the same liposome concentration in the hydrogel dictates different weight/volume ratios for these two lipids.
The results of the friction coefficient measurements described hereinabove are summarized in Tables 23-26 below.
TABLE 23
T = 25°
HEMA hydrogels EGDMA = 0.22%
neat
SUV DMPC
SUV HSPC
Load [Kg]
0 mM
2 mM
4 mM
12 mM
2 mM
4 mM
12 mM
0.04
0.2 ± 0.01
0.12 ± 0.01
0.014 ± 0.005
0.017 ± 0.003
0.2 ± 0.01
0.015 ± 0.005
0.022 ± 0.005
0.15
0.5 ± 0.01
47 ± 0.01
0.017 ± 0.005
0.016 ± 0.003
0.016 ± 0.005
0.022 ± 0.005
0.5
0.013 ± 0.005
0.02 ± 0.005
TABLE 24
T = 25°
HEMA hydrogels EGDMA = 1%
neat
SUV DMPC
SUV HSPC
Load [Kg]
0 mM
2 mM
12 mM
2 mM
12 mM
0.04
0.27 ± 0.008
0.02 ± 0.005
0.0058 ± 0.003
0.039 ± 0.005
0.037 ± 0.005
0.15
0.33 ± 0.009
0.015 ± 0.005
0.0046 ± 0.003
0.021 ± 0.005
0.029 ± 0.005
0.5
0.067 ± 0.005
0.0075 ± 0.005
0.02 ± 0.005
0.029 ± 0.005
1
0.042 ± 0.005
0.0085 ± 0.005
0.02 ± 0.005
3
0.013 ± 0.005
TABLE 25
T = 37°
HEMA hydrogels EGDMA = 0.22%
neat
SUV DMPC
SUV HSPC
Load [Kg]
0 mM
2 mM
4 mM
12 mM
2 mM
4 mM
12 mM
0.04
0.183 ± 0.007
0.3 ± 0.009
0.2 ± 0.007
0.03 ± 0.007
0.08 ± 0.005
0.03 ± 0.005
0.068 ± 0.005
0.15
0.32 ± 0.01
0.21 ± 0.009
0.25 ± 0.007
0.085 ± 0.007
0.095 ± 0.005
0.08 ± 0.005
0.064 ± 0.005
0.5
0.19 ± 0.007
0.26 ± 0.007
0.107 ± 0.005
0.044 ± 0.005
0.054 ± 0.005
1
0.15 ± 0.007
0.2 ± 0.007
0.07 ± 0.005
0.057 ± 0.005
0.056 ± 0.005
TABLE 26
T = 37°
HEMA hydrogels EGDMA = 1%
neat
SUV DMPC
SUV HSPC
Load [Kg]
0 mM
2 mM
12 mM
2 mM
12 mM
0.04
0.272 ± 0.01
0.3 ± 0.008
0.0033 ± 0.003
0.047 ± 0.005
0.07 ± 0.005
0.15
0.34 ± 0.01
0.2 ± 0.009
0.003 ± 0.003
0.03 ± 0.005
0.07 ± 0.005
0.5
0.015 ± 0.005
0.032 ± 0.005
0.06 ± 0.005
1
0.038 ± 0.005
0.022 ± 0.005
0.06 ± 0.005
Varying Concentration of Multilamellar Vesicles (MLVs):
HEMA hydrogels were prepared with different MLV HSPC and MLV DMPC liposome concentration that were incorporated inside the hydrogels as described hereinabove.
TABLE 27
T = 25°
HEMA hydrogels EGDMA = 0.1%
neat
MLV DMPC
MLV HSPC
Load [Kg]
0 mM
2 mM
18 mM
2 mM
18 mM
0.04
0.2 ± 0.01
0.059 ± 0.005
0.068 ± 0.005
0.04 ± 0.005
0.035 ± 0.005
0.15
0.2 ± 0.01
0.095 ± 0.005
0.066 ± 0.005
0.159 ± 0.01
0.033 ± 0.005
0.5
0.142 ± 0.03
0.058 ± 0.005
0.07 ± 0.008
1
0.045 ± 0.005
TABLE 28
T = 25°
HEMA hydrogels EGDMA = 1%
neat
MLV DMPC
MLV HSPC
Load [Kg]
0 mM
2 mM
18 mM
2 mM
18 mM
0.04
0.27 ± 0.008
0.0152 ± 0.008
0.011 ± 0.005
0.014 ± 0.005
0.04 ± 0.006
0.15
0.33 ± 0.009
0.053 ± 0.01
0.015 ± 0.006
0.012 ± 0.005
0.025 ± 0.005
0.5
0.11 ± 0.01
0.015 ± 0.006
0.03 ± 0.007
0.0185 ± 0.005
1
0.021 ± 0.006
0.012 ± 0.007
0.014 ± 0.005
3
0.03 ± 0.009
0.05 ± 0.01
5
0.036 ± 0.013
7
0.0350.014
TABLE 29
T = 25°
HEMA hydrogels EGDMA = 2%
neat
MLV DMPC
MLV HSPC
Load [Kg]
0 mM
2 mM
18 mM
2 mM
18 mM
0.04
0.6 ± 0.05
0.2 ± 0.03
0.03 ± 0.01
0.028 ± 0.005
0.03 ± 0.008
0.15
0.6 ± 0.05
0.5 ± 0.05
0.01 ± 0.003
0.025 ± 0.005
0.025 ± 0.007
0.5
0.01 ± 0.003
0.03 ± 0.005
0.014 ± 0.004
1
0.01 ± 0.003
0.02 ± 0.005
0.01 ± 0.005
3
0.01 ± 0.003
0.05 ± 0.005
0.01 ± 0.005
5
0.011 ± 0.0038
7
0.012 ± 0.005
TABLE 30
T = 37°
HEMA hydrogels EGDMA = 0.1%
neat
MLV DMPC
MLV HSPC
Load
0 mM
2 mM
18 mM
2 mM
18 mM
0.04
0.27 ± 0.03
0.21 ± 0.005
0.118 ± 0.01
0.023 ± 0.005
0.03 ± 0.005
0.15
0.27 ± 0.03
0.26 ± 0.005
0.2 ± 0.03
0.158 ± 0.01
0.026 ± 0.005
0.5
0.15 ± 0.03
0.03 ± 0.005
1
0.056 ± 0.005
TABLE 31
T = 37°
HEMA hydrogels EGDMA = 1%
neat
MLV DMPC
MLV HSPC
Load [Kg]
0 mM
2 mM
18 mM
2 mM
18 mM
0.04
0.272 ± 0.01
0.075 ± 0.008
0.07 ± 0.01
0.02 ± 0.008
0.025 ± 0.005
0.15
0.34 ± 0.01
0.055 ± 0.008
0.062 ± 0.01
0.03 ± 0.008
0.015 ± 0.005
0.5
0.05 ± 0.008
0.05 ± 0.01
0.074 ± 0.008
0.014 ± 0.005
1
0.03 ± 0.008
0.04 ± 0.015
0.03 ± 0.008
0.017 ± 0.005
3
0.08 ± 0.008
0.038 ± 0.013
TABLE 32
T = 37°
HEMA hydrogels EGDMA = 2%
neat
MLV DMPC
MLV HSPC
Load [Kg]
0 mM
2 mM
18 mM
2 mM
18 mM
0.04
0.6 ± 0.05
0.056 ± 0.008
0.04 ± 0.01
0.056 ± 0.01
0.04 ± 0.01
0.15
0.5 ± 0.05
0.047 ± 0.008
0.03 ± 0.015
0.034 ± 0.007
0.01 ± 0.005
0.5
0.1 ± 0.008
0.033 ± 0.013
0.026 ± 0.006
0.0118 ± 0.005
1
0.077 ± 0.008
0.035 ± 0.015
0.107 ± 0.02
0.014 ± 0.005
3
0.078 ± 0.008
0.035 ± 0.013
0.365 ± 0.05
0.016 ± 0.005
The results of the friction coefficient measurements described hereinabove are summarized in Tables 27-32 below.
HEMA hydrogels with 0.22% and 1% crosslinking, incorporating SUV DMPC liposomes at a concentration ≤2 mM showed relatively high μ values compared with similar hydrogels having liposomes at a concentration of 12 mM. Hydrogels with low concentrations of SUV HSPC (<2 mM) showed relatively low μ values.
HEMA hydrogels with 0.1% and 2% crosslinking incorporating MLV HSPC or MLV DMPC liposomes showed an increase in μ value when liposome concentration was reduced from about 18 mM to about 2 mM and below.
HEMA hydrogels with 1% crosslinking, incorporating MLV liposomes showed an increase in μ values at liposomes concentration between 0.4 to 2 mM, depending on the lipid species and the temperature of the measurement.
The effect of adding methacrylic acid (MA or MAAc) to the hydrogel during the HEMA hydrogel/liposome preparation was tested.
Hydrogel Preparation:
Neat hydrogels were prepared as follows: HEMA (1.425 grams), EGDMA at 0.75% (molar percent with respect to the HEMA monomer), methacrylic acid (MA, 75 mg) and APS aqueous solution (2 ml, 53 mM) were vigorously stirred for 30 minutes until fully mixed. TMEDA (50 μl) was added to the mixture, stirred for 20 seconds and poured into a 6 cm diameter petri dish. The gels were allowed to cure over 4-5 hours, followed by rinsing in distilled water for 3 days to remove unreacted materials. The obtained gels were cut into pieces for tribological tests and other characterization methods. Liposome-loaded hydrogels were prepared similarly. The APS aqueous solution was replaced by a liposome suspension with the same APS content.
Hydrogel Water Content:
The water adsorbed by a hydrogel is quantitatively represented by the equilibrium water content (EWC) which is the ratio of the weight of water in the hydrogel to the weight of the hydrogel at equilibrium hydration. The weight of water in the hydrogel is the difference between the weight of the hydrated hydrogel to the dry gel.
The gel in its hydrated form was weighed and then put in an oven until complete dryness of the sample to give its dry weight. EWC of The HEMA-MA neat hydrogel was found to be about 84%, and the EWC of the HEMA-MA hydrogels with liposomes (either MLV DMPC or MLV HSPC) was found to be about 82%.
Dynamic Mechanical Characterization of Hydrogels:
Samples were subjected to a strain sweep test in which they were deformed at different shear strains, and the moduli were recorded to define the linear viscoelastic zone in which the modulus G′ is independent of the applied strain. Each sample was then subjected to a frequency sweep test. A sinusoidal deformation of constant peak amplitude was applied over the range of frequencies from 0.05-20 Hz under a stress of 5 Pa at 20° C.
Table 33 presents the results of the frequency sweep at 1 Hz test of a HEMA-MA hydrogels, based on two independent measurements of each hydrogel.
TABLE 33
G′ [Pa]
G″ [Pa]
neat HEMA-MA
5300
935
HEMA-MA MLV HSPC 30 mM
9300
1330
HEMA-MA MLV HSPC 20 mM
4100
930
HEMA-MA MLV DMPC 30 mM
3580
740
Friction Measurements Hydrogel vs. Metal Head:
Friction forces were measured between the different HEMA-MA hydrogels to a metal head at amplitudes of 1 mm, sliding velocity of 1 mm/sec. Friction coefficient was calculated based on 2-4 measurements from different contact area taken from a 1-2 independent hydrogels preparations.
The results, presented in
Changing the concentration of MLV HSPC liposomes from 30 mM to 20 mM and 10 mM showed a connection between concentration and friction coefficient μ. At concentration of 10 mM MLV HSPC liposomes no shear reduction was observed compared with the neat hydrogel.
TABLE 34
25° C.
10 g load
40 g load
150 g load
300 g load
500 g load
HEMA-AA
0.26 ± 0.02
#
neat
HEMA-AA
0.05 ± 0.005
0.05 ± 0.005
0.05 ± 0.005
0.04 ± 0.005
0.04 ± 0.005
MLV HSPC 30 mM
HEMA-AA
0.062 ± 0.005
0.06 ± 0.005
0.063 ± 0.005
0.068 ± 0.005
#
MLV HSPC 20 mM
HEMA-AA
0.4 ± 0.02
#
MLV HSPC 10 mM
HEMA-AA
0.26 ± 0.02
#
MLV DMPC 30 mM
TABLE 35
37° C.
10 g load
40 g load
150 g load
300 g load
500 g load
HEMA-AA
0.19 ± 0.02
#
neat
HEMA-AA
0.04 ± 0.005
0.04 ± 0.005
0.031 ± 0.005
0.025 ± 0.005
0.022 ± 0.005
MLV HSPC 20 mM
This study investigated the use of the hydrogel-forming agent methacrylamide (MMA or MAAm) and the crosslinking agent polyethyleneoxide dimethacrylate (also known as poly(ethylene glycol) dimethacrylate, PEOdMA or pEGDMA) in the formation of the hydrogel. In this example, the crosslinking agent was 9EGDMA, or (ethylene glycol)9 dimethacrylate.
Methacrylamide (MMA) and the PEOdMA (ethylene glycol)9 dimethacrylate (9EGDMA) having a MW of 550, were purchased from Sigma-Aldrich and used as received.
Hydrogel Preparation:
Hydrogels with initial methacrylamide concentration of 31% by weight and PEOdMA at a concentration of 7.8 molar % were prepared by photo-initiated radical crosslinking in the presence of the water soluble photoinitiator Irga 2959 0.3% by weight. The hydrogels solutions were stirred till the solution turned clear, and then they were poured to a 6 glass petri dish. The samples were cured by exposure to UV light for 15 minutes. For preparation of hydrogels containing liposomes, pure water was replaced with either MLV DMPC or MLV HSPC of concentration of 39 mM.
Hydrogel Water Content:
Hydrogels in their hydrated form were weighed and then put in an oven until complete dryness of the sample afforded the dry weight. EWC of the MAA-PEOdMA neat hydrogel was found to be 66.6%, and the EWC of the MAA-PEOdMA hydrogels with MLV DMPC or MLV HSPC liposomes was 67.5% and 65%, respectively.
Dynamic Mechanical Characterization of Hydrogels:
Samples were subjected to a strain sweep test in which they were deformed at different shear strains, and the moduli were recorded to define the linear viscoelastic zone in which the modulus G′ is independent of the applied strain. Each sample was then subjected to a frequency sweep test. A sinusoidal deformation of constant peak amplitude was applied over the range of frequencies from 0.05-100 Hz under a stress of 20 Pa at 25° C.
Table 36 presents the results of the frequency sweep at 1 Hz test of a MAA hydrogels.
TABLE 36
G′ [Pa]
G″ [Pa]
MMA-PEOdMA neat
3.8 × 104
1 × 103
MMA-PEOsMA MLV HSPC mM
8.2 × 104
5 × 103
MMA-PEOsMA MLV DMPC mM
7.6 × 104
3.2 × 103
Friction Measurements Hydrogel vs. Metal Head:
Friction forces were measured between the different MAA-PEOdMA hydrogels against a metal head at amplitudes of 1 mm, sliding velocity of 1 mm/sec. Friction coefficient was calculated based on 4 measurements from 2 different contact area taken from a 2 independent hydrogels preparations for the neat and the DMPC incorporated liposomes, and of 2 measurements of different contact points taken from the same hydrogel for the HSPC incorporated liposomes.
At temperature of 25° C. the incorporation of DMPC liposomes into the MAA-PEOdMA hydrogels reduced friction coefficient from μ=0.13 to μ=0.02 or 0.0245, a reduction of a factor of about 5. The incorporation of HSPC liposomes showed a reduction in the friction coefficient of a factor of about 4. Heating the experimental system to temperature of 37° C. showed a reversed trend as the DMPC MAA-PEOdMA hydrogels showed no efficient shear reduction and the HSPC MAA-PEOdMA hydrogels reduced friction coefficient up to a factor of 5.
Table 37 presents the results of the friction coefficient measured at 25° C. between different MAA-PEOdMA hydrogels against a metal head at amplitudes of 1 mm.
TABLE 37
25° C.
40 g load
150 g load
500 g load
MAA-PEOdMA
0.13 ± 0.04
0.121 ± 0.01
0.12 ± 0.005
neat
MAA-PEOdMA
0.02 ± 0.007
0.020.008
0.0245 ± 0.01
MLV DMPC
MAA-PEOdMA
0.03 ± 0.01
0.03 ± 0.01
0.03 ± 0.01
MLV HSPC
Table 38 presents the results of the friction coefficient measured at 37° C. between different MAA-PEOdMA hydrogels against a metal head at amplitudes of 1 mm.
TABLE 38
37° C.
40 g load
150 g load
500 g load
MAA-PEOdMA
0.069 ± 0.02
0.1 ± 0.02
0.08 ± 0.01
neat
MAA-PEOdMA
0.084 ± 0.03
0.093 ± 0.02
0.073 ± 0.01
MLV DMPC
MAA-PEOdMA
0.02 ± 0.01
0.02 ± 0.01
0.019 ± 0.01
MLV HSPC
The use of acrylamide (AA or AAm) and N,N-dimethacrylamide (nnDMAA) as the hydrogel-forming agents was studied.
Acrylic acid (AA), N,N-dimethacrylamide (nnDMAA), crosslinking agent N,N-methylenebis(acrylamide) (MBA or MBAm), ammonium persulfate (APS), and N,N,N′,N′-tetramethylethylenediamine (TMEDA), were purchased from Sigma-Aldrich and used as received.
Hydrogel Preparation:
Neat hydrogels were prepared as follows: AA and nnDMAA were mixed in different molar ratios of 1:1 (G1), 1:2 (G2) and 2:1 (G3) in 0.5% (w/v) of APS and 0.2% (w/v) of MBA. Total monomers concentration was of 20% (v/v). Hydrogel with 40% of monomer concentration (v/v) at 1:1 molar ratio was prepared as well (G4). Hydrogels encapsulating liposomes were prepared by replacing the pure water with liposome suspension of MLV DMPC at 45 mM. All hydrogels were vigorously stirred for 30 minutes until fully mixed. TMEDA (50 μl) was added to the mixture, stirred for 20 seconds and poured into a 6 cm diameter petri dish and the hydrogels were placed on a hot plate of 35° C. for 3-5 minutes. The hydrogels were allowed to cure over 4-5 hours, followed by rinsing in distilled water for 3 days to remove unreacted materials. The obtained hydrogels were cut into pieces for tribological tests and other characterization methods. Liposome-loaded hydrogels were prepared similarly. The APS aqueous solution was replaced by a liposome suspension with the same APS content.
Hydrogels in their hydrated form were weighed and then put in an oven until complete dryness of the sample afforded the dry weight. EWC of The G1, G2 and G3 AA-nnDMAA neat hydrogels was found to be about 98% and G4 AA-nnDMAA neat hydrogel water content was found to be about 92%. For the DMPC incorporated hydrogels, EWC of G1, G2 and G3 was about 98%, and for G4 about 91%.
Dynamic Mechanical Characterization of Hydrogels:
Samples were subjected to a strain sweep test in which they were deformed at different shear strains, and the moduli were recorded to define the linear viscoelastic zone in which the modulus G′ is independent of the applied strain. Each sample was then subjected to a frequency sweep test. A sinusoidal deformation of constant peak amplitude was applied over the range of frequencies from 0.05-20 Hz under a stress of 2 Pa at 25° C.
Table 39 presents the result of the frequency sweep at 1 Hz test for the AA-nnDMAA hydrogels.
TABLE 39
G′ [Pa]
G″ [Pa]
G1 AA-nnDMAA
423
50
neat
G2 AA-nnDMAA
80
33
neat
G3 AA-nnDMAA
1066
118
neat
G4 AA-nnDMAA
186
66
neat
G1 AA-nnDMAA
625
93
MLV DMPC 45 mM
G2 AA-nnDMAA
1728
146
MLV DMPC 45 mM
G3 AA-nnDMAA
783
70
MLV DMPC 45 mM
G4 AA-nnDMAA
90
73
MLV DMPC 45 mM
Friction Measurements Hydrogel vs. Metal Head:
Friction forces were measured between the AA-nnDMAA hydrogels against a metal head at amplitudes of 1 mm, sliding velocity of 1 mm/sec. Friction coefficient was calculated based on 2 from different contact area, and the results are presented in Table 40.
TABLE 40
Results at 37°
10 g
40 g
G1 AA-nnDMAA
#
#
neat
G2 AA-nnDMAA
#
#
neat
G3 AA-nnDMAA
#
#
neat
G4 AA-nnDMAA
#
#
neat
G1 AA-nnDMAA
#
#
MLV DMPC
G2 AA-nnDMAA
0.0125 ± 0.007
#
MLV DMPC
G3 AA-nnDMAA
0.013 ± 0.007
#
MLV DMPC
G4 AA-nnDMAA
0.012 ± 0.007
#
MLV DMPC
As can be seen in Table 40, the incorporation of MLV DMPC liposomes inside the AA-nnDMAA hydrogels decrease friction coefficient from a rigid coupling for the neat hydrogels G1-G4 to μ=0.012-0.013 for the G2-G4 hydrogel with the 45 mM MLV DMPC. The friction coefficient of the G1 hydrogel did not decrease upon adding liposomes, as the shear trace reveal a rigid coupling scenario. Above a load of 10 g the hydrogel with the incorporated liposomes turn into rigid coupling.
The effect of incorporation of liposomes into gelatin methacrylate hydrogels on the mechanical properties of these hydrogels was tested.
Materials:
Phosphate buffer, sodium hydroxide, methacrylic anhydride and gelatin (type A from porcine skin) and 2-hydroxy-4′-(2-hydroxyethoxy)-2-methylpropiophenone (Irga 2959) were purchased from Sigma Aldrich.
Dialysis was conducted using dialysis membrane (MWCO 12 kDa-14 kDa) from CelluSep membranes.
Synthesis of Methacrylated Gelatin:
Gelatin methacrylate (GM) was synthesized as previously described [Van Den Bulcke, A. I., et al., Biomacromolecules, 2000, 1(1), p. 31-38]. Briefly, gelatin (4 grams) was dissolved in phosphate buffer (40 ml, pH 7.4) at 40° C. The pH of the solution was then adjusted to 7.5 using NaOH solution. 2 ml of methacrylic anhydride was added drop wise after gelatin was completely dissolved. During the methacrylation reaction the mixture was stirred and the pH of the solution was kept at the range of 7-7.5 for two hours of reaction time at 50° C. for 30 minutes. Thereafter, the mixture was diluted with PBS and dialyzed for 2 days against distilled water at 40° C. The reaction product was freeze-dried and stored at −20° C. until use.
Liposomes Preparation:
Multilamellar vesicles (MLV) composed of 1,2-dimyristoyl-sn-glycero-3-phosphocholine (DMPC) and hydrogenated soy phosphatidylcholine (HSPC) were prepared by hydrating the lipids in at least 5° C. above the lipid TM, followed by sonication.
Hydrogel Preparation:
Hydrogels with initial gelatin methacrylate concentration of 20% by weight were prepared by photo-initiated radical crosslinking in the presence of the water soluble photoinitiator Irga 2959. The hydrogels solutions were stirred and heated to 40° C. until the solution turned clear, and then poured to a glass petri dish. Hydrogels with liposomes were prepared by replacing water with 45 mM MLV DMPC liposome suspension. The samples were cured by exposure to UV light for 15 minutes.
Rheological Measurements:
Dynamic rheological tests were performed to characterize the visco-elastic properties of the gelatin methacrylate hydrogels. The measurements were carried out using a mars III rheometer, using a parallel plate model.
Friction Measurements:
Round samples of diameter of 21 mm were cut from the GM hydrogels and were glued onto a plastic petri dish. The plastic petri dish was filled with water and the system was heated to 37° C.±0.5° C. Friction force was measured between the GM hydrogels to a metal head of diameter of 28 mm. Friction tests were carried out using a UMT nano-bruker tribometer. A normal load of 10 grams was applied, the lateral force (Fs) was measured and the friction coefficient was calculated according to μ=Fs/Fn.
Determination of Degree of Methacrylation:
Samples of 30 mg of GM and unmodified gelatin were dissolved each in 500 μL of deuterium oxide and the level of methacrylation of gelatin was analyzed using 1H NMR spectroscopy.
Compared to the unmodified gelatin, new peaks were observed in the NMR spectra of the GM at 5.3 ppm≤δ≤6.2 ppm. These peaks were assigned to the methyl function of the introduced methacrylic groups. The degree of methacrylation was defined as the percentage of the amino acid lysine that was modified. For the quantification of the degree of methacrylation, the NMR spectrum was normalized to the signal of the phenylalanine (6.9-7.5 ppm), which represents the concentration of gelatin. Thereafter, the GM spectra were integrated to obtain the areas A, and the degree of methacrylation (DM) was determined by: DM(%)=(1−A(Lysine methylene of GM)/A(Lysine methylene of unmodified gelatin)). The DM was calculated to be 75% (about 1.3% in terms of degree of crosslinking, or molar percent of a crosslinking agent to hydrogel-forming agent).
Dynamic Mechanical Properties Measurements:
Samples were subjected to a strain sweep test in which they were deformed at different shear strains, and the moduli were recorded to define the linear viscoelastic zone in which the modulus G′ is independent of the applied strain. Each sample was then subjected to a frequency sweep test. A sinusoidal deformation of constant peak amplitude was applied over the range of frequencies from 0.05-20 Hz under a stress of 20 Pa at 25° C. and 37° C.
Table 41 presents the results of the friction coefficient measured at 25° C. and 37° C. of the frequency sweep at 1 Hz test of the Gelatin-MA hydrogels.
TABLE 41
G′ [Pa]
G″ [Pa]
G′ [Pa]
G″ [Pa]
T = 25° C.
T = 25° C.
T = 37° C.
T = 37° C.
Gelatin-MA
3752
97
4730
451
neat
Gelatin-MA +
8000
390
7600
524
MLV DMPC
Hydrogel Water Content:
The equilibrium water content (EWC) of gelatin-methacrylate hydrogels were determined as described hereinabove. EWC of the neat gelatin-MA hydrogels was about 82%, and the EWC of the DMPC gelatin-MA hydrogels was about 86%.
Friction Coefficient Measurements:
Friction forces were measured between the gelatin-MA hydrogels against a metal head at amplitudes of 1 mm in pure water at temperature of 37° C. Friction coefficient was calculated based on 2 measurements from different contact area.
The neat gelatin-MA hydrogels showed that already at normal load of 10 grams after about 2-3 minutes of shearing, the trace was of a rigid coupling, meaning that there was no sliding in the hydrogel-metal interface, and that the two parts were moving together. The probe that monitored the height of the sample showed that under load of 10 grams at T=37° C. after about 130 seconds from the beginning of shearing, there was a dramatic decrease in the height of the sample which is accompanied by the rigid coupling trace.
The gelatin-MA hydrogels with the incorporation of MLV DMPC liposomes show that the friction coefficient at load of 10 grams is of μ=0.056±0.02. The height of the hydrogel sample with the liposomes during the measurement is constant over a running period of one hour, indicating of improved wear as well as reduction of μ.
Shearing the gelatin-MA hydrogel over a range of velocities indicates that the friction coefficient is not a function of the sliding velocity when velocity range from 0.01 mm per second to 5 mm per second. This may implies that the lubrication mechanism of the hydrogel is that of boundary lubrication rather than a hydrodynamic effect, which may be related to the incorporation of the liposomes into the hydrogel.
This study investigates the influence of inclusion of cholesterol at varying concentrations into the lipid composition of the liposomes, on the properties of hydrogels encapsulating these liposomes at different measurement temperatures of 25° C. and 37° C.
The exemplary liposomes which were prepared were SUV DPPC, MLV DMPC and MLV HSPC having cholesterol at an amount of 0%, 5%, 10%, 15% and 40% in terms of molar percentage, relative to the total amount of liposome lipids.
Cholesterol-containing MLV DMPC and MLV HSPC liposomes were incorporated into HEMA EGDMA 2% hydrogels for friction coefficient measurements against a metal head.
Cholesterol-containing SUV DPPC liposomes with cholesterol levels of 0%, 5%, 15% and 40% were incorporated into HEMA EGDMA 1% and 2% and were tested as well.
Liposomes concentration inside the hydrogel solution before curing was 18 mM for the MLV liposomes, and 10.5 mM for the SUV liposomes.
Friction Coefficient for HEMA EGDMA2% with MLV of DMPC and HSPC with Cholesterol:
Table 42 also presents the friction coefficient measurements shown in
TABLE 42
HEMA EGDMA 2% + MLV HSPC/Cholesterol, T = 25° C.
Load
10%
15%
40%
[Kg]
0% cholesterol
cholesterol
cholesterol
cholesterol
0.04
0.02 ± 0.005
0.02 ± 0.005
0.014 ± 0.005
0.273 ± 0.01
0.15
0.025 ± 0.007
0.015 ± 0.005
0.016 ± 0.005
0.22 ± 0.008
0.5
0.014 ± 0.005
0.02 ± 0.005
0.018 ± 0.005
0.18 ± 0.01
1
0.01 ± 0.005
0.02 ± 0.005
0.015 ± 0.005
0.06 ± 0.005
3
0.01 ± 0.005
0.018 ± 0.005
0.035 ± 0.005
As can be seen in
Table 43 presents the friction coefficient measurements shown in
TABLE 43
HEMA EGDMA 2% + MLV DMPC/Cholesterol, T = 25° C.
Load
10%
15%
40%
[Kg]
0% cholesterol
cholesterol
cholesterol
cholesterol
0.04
0.01 ± 0.005
0.015 ± 0.005
0.015 ± 0.005
0.027 ± 0.005
0.15
0.01 ± 0.005
0.029 ± 0.005
0.04 ± 0.005
0.02 ± 0.005
0.5
0.01 ± 0.005
0.0395 ± 0.005
0.066 ± 0.005
0.03 ± 0.005
1
0.01 ± 0.005
0.03 ± 0.005
0.049 ± 0.005
0.03 ± 0.005
3
0.01 ± 0.005
0.037 ± 0.005
0.033 ± 0.005
0.028 ± 0.005
5
0.011 ± 0.005
5
0.012 ± 0.005
As can be seen in
Table 44 presents the friction coefficient measurements shown in
TABLE 44
HEMA EGDMA 2% + MLV HSPC/Cholesterol, T = 37° C.
10%
15%
40%
Load [Kg]
0% cholesterol
cholesterol
cholesterol
cholesterol
0.04
0.034 ± 0.007
0.024 ± 0.005
0.045 ± 0.01
0.16 ± 0.01
0.15
0.01 ± 0.005
0.025 ± 0.005
0.05 ± 0.01
0.2 ± 0.01
0.5
0.012 ± 0.005
0.027 ± 0.005
0.052 ± 0.01
0.18 ± 0.01
1
0.014 ± 0.005
0.015 ± 0.005
0.047 ± 0.01
0.1 ± 0.01
3
0.016 ± 0.005
As can be seen in
Table 45 presents the friction coefficient measurements shown in
TABLE 45
HEMA EGDMA 2% + MLV DMPC/Cholesterol, T = 37° C.
Load
10%
15%
40%
[Kg]
0% cholesterol
cholesterol
cholesterol
cholesterol
0.04
0.02 ± 0.01
0.007 ± 0.003
0.066 ± 0.01
0.9 ± 0.1
0.15
0.02 ± 0.01
0.005 ± 0.003
0.094 ± 0.01
0.66 ± 0.02
0.5
0.025 ± 0.01
0.0067 ± 0.003
0.0106 ± 0.01
1
0.035 ± 0.01
0.0042 ± 0.003
0.083 ± 0.01
3
0.035 ± 0.01
0.0087 ± 0.003
0.066 ± 0.01
5
0.01 ± 0.005
0.06 ± 0.01
As can be seen in
Hence, it can be seen that incorporation of cholesterol inside MLV HSPC and measurements at both temperatures of 25° C. and 37° C. had a relatively small effect at low cholesterol concentrations of 10% and 15%, and for higher cholesterol concentration of 40% , the friction coefficient relatively increased. Incorporation of cholesterol inside MLV DMPC and measurements at temperature of 37° C. decreased friction for the low cholesterol concentration of 10% and increased friction coefficient for the higher cholesterol levels.
Friction Coefficient of HEMA EGDMA 1% and 2% with SUV DPPC with Cholesterol:
SUV DPPC liposomes were prepared with different cholesterol concentrations of 0%, 5%, 15% and 40% relative to the total amount of lipid composition of the liposome. Friction coefficients of HEMA hydrogels with 1% and 2% molar percent of EGDMA crosslinking agent, and containing SUV DPPC/cholesterol were measured and calculated using a tribometer.
Tables 46, 47, 48 and 49 summarize the results presented in
TABLE 46
HEMA EGDMA 1% + SUV DPPC/Cholesterol, T = 25° C.
15%
40%
Load [Kg]
0% cholesterol
5% cholesterol
cholesterol
cholesterol
0.04
0.03 ± 0.005
0.031 ± 0.007
0.28 ± 0.07
0.23 ± 0.07
0.15
0.02 ± 0.005
0.14 ± 0.008
0.32 ± 0.07
0.3 ± 0.07
0.5
0.02 ± 0.005
0.156 ± 0.008
1
0.036 ± 0.005
TABLE 47
HEMA EGDMA 2% + SUV DPPC/Cholesterol, T = 25° C.
Load
15%
40%
[Kg]
0% cholesterol
5% cholesterol
cholesterol
cholesterol
0.04
0.04 ± 0.005
0.01 ± 0.005
0.2 ± 0.01
0.24 ± 0.03
0.15
0.025 ± 0.005
0.009 ± 0.005
0.21 ± 0.01
0.19 ± 0.01
0.5
0.018 ± 0.005
0.008 ± 0.005
0.16 ± 0.01
0.16 ± 0.01
1
0.018 ± 0.005
0.016 ± 0.005
0.135 ± 0.005
0.11 ± 0.01
TABLE 48
HEMA EGDMA 1% + SUV DPPC/Cholesterol, T = 37° C.
Load
15%
40%
[Kg]
0% cholesterol
5% cholesterol
cholesterol
cholesterol
0.04
0.009 ± 0.005
0.009 ± 0.005
0.017 ± 0.005
0.013 ± 0.005
0.15
0.013 ± 0.005
0.011 ± 0.005
0.018 ± 0.005
0.08 ± 0.01
0.5
0.015 ± 0.005
0.01 ± 0.005
0.011 ± 0.005
1
0.035 ± 0.005
0.016 ± 0.005
0.027 ± 0.007
3
0.018 ± 0.005
0.036 ± 0.008
TABLE 49
HEMA EGDMA 2% + SUV DPPC/Cholesterol, T = 37° C.
15%
40%
Load [Kg]
0% cholesterol
5% cholesterol
cholesterol
cholesterol
0.04
0.039 ± 0.008
0.013 ± 0.005
0.07 ± 0.01
0.31 ± 0.01
0.15
0.068 ± 0.008
0.03 ± 0.005
0.11 ± 0.01
0.27 ± 0.01
0.5
0.064 ± 0.008
0.047 ± 0.005
0.11 ± 0.01
0.21 ± 0.01
1
0.034 ± 0.008
0.1 ± 0.005
0.14 ± 0.01
0.17 ± 0.01
As can be seen in
In general, it can be summarized that that the effect of the addition of low levels (5-10%) of cholesterol to liposomes encapsulated in a hydrogel, is a decrease in the observed friction coefficient μ compared to corresponding hydrogels containing high levels (40%) of cholesterol, for which μ is increased, depending on the lipid specie and the temperature.
Specifically, adding cholesterol into MLV HSPC liposomes that were incorporated in HEMA EGDMA 2% hydrogels at low levels (10% and 15% at T=25° C. and 10% for T=37° C., did not affect friction coefficient μ. Higher levels of cholesterol than the above result in an increase of μ.
Adding 10%, 15% and 40% cholesterol into MLV HSPC liposomes that were incorporated in HEMA EGDMA 2% hydrogels, resulted in an increasing μ at T=25° C. At T=37° C. adding 10% (low level) of cholesterol resulted in a decrease of μ, and increasing cholesterol levels to 15% and 40% result in an increasing μ.
Adding cholesterol into SUV DPPC liposomes that were incorporated into HEMA hydrogels with 1% or 2% of crosslinking agent showed that for the 1% crosslinking level adding cholesterol increased μ at T=25° C. At T=37° C. adding low level of cholesterol (5% and 15%) did not have a notable effect on μ, while at higher levels of cholesterol (40%) μ increased. For the 2% crosslinking level, adding 15% and 40% cholesterol increased μ, while adding 5% cholesterol to the liposomes decreases μ at the low loads region and at T=37° C. and at the high loads region for T=25° C.
Although the invention has been described in conjunction with specific embodiments thereof, it is evident that many alternatives, modifications and variations will be apparent to those skilled in the art. Accordingly, it is intended to embrace all such alternatives, modifications and variations that fall within the spirit and broad scope of the appended claims.
All publications, patents and patent applications mentioned in this specification are herein incorporated in their entirety by reference into the specification, to the same extent as if each individual publication, patent or patent application was specifically and individually indicated to be incorporated herein by reference. In addition, citation or identification of any reference in this application shall not be construed as an admission that such reference is available as prior art to the present invention. To the extent that section headings are used, they should not be construed as necessarily limiting. In addition, any priority document(s) of this application is/are hereby incorporated herein by reference in its/their entirety.
Klein, Jacob, Goldberg, Ronit, Iuster, Noa, Sorkin, Raya
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